EP1648553A2 - Appareil et procede de stimulation bioelectrique, d'acceleration de la cicatrisation, de soulagement de la douleur ou de devitalisation d'agents pathogenes - Google Patents

Appareil et procede de stimulation bioelectrique, d'acceleration de la cicatrisation, de soulagement de la douleur ou de devitalisation d'agents pathogenes

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Publication number
EP1648553A2
EP1648553A2 EP04755993A EP04755993A EP1648553A2 EP 1648553 A2 EP1648553 A2 EP 1648553A2 EP 04755993 A EP04755993 A EP 04755993A EP 04755993 A EP04755993 A EP 04755993A EP 1648553 A2 EP1648553 A2 EP 1648553A2
Authority
EP
European Patent Office
Prior art keywords
primary
recited
intervals
cycle
timing
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
EP04755993A
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German (de)
English (en)
Other versions
EP1648553A4 (fr
Inventor
James W. Kronberg
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Medrelief Inc
Original Assignee
Healthonics Inc
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Filing date
Publication date
Application filed by Healthonics Inc filed Critical Healthonics Inc
Publication of EP1648553A2 publication Critical patent/EP1648553A2/fr
Publication of EP1648553A4 publication Critical patent/EP1648553A4/fr
Ceased legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36014—External stimulators, e.g. with patch electrodes
    • A61N1/36021—External stimulators, e.g. with patch electrodes for treatment of pain
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/025—Digital circuitry features of electrotherapy devices, e.g. memory, clocks, processors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/326—Applying electric currents by contact electrodes alternating or intermittent currents for promoting growth of cells, e.g. bone cells
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
    • A61N1/3606—Implantable neurostimulators for stimulating central or peripheral nerve system adapted for a particular treatment
    • A61N1/36071—Pain

Definitions

  • the present invention relates to a pulsed signal generator for biomedical applications.
  • the present invention relates to a light-weight, compact pulsed signal generator that produces unique output waveforms based on a plurality of relatively long primary timing intervals Tl, T2 and so forth, forming in succession a primary repeating cycle; a plurality of shorter secondary timing intervals tl, t2 and so forth, into which at least one of said primary intervals is divided, and forming in succession a secondary repeating cycle which continues throughout the length of that primary interval, while at least one other of said primary intervals is not so divided; a plurality of constant voltage or current levels Ll, L2 and so forth, one of which is selected during each primary or secondary timing interval.
  • the output waveform comprises an equalizing pulse immediately following the pulse burst.
  • the output waveform comprises a gradual step-in and step- out period optionally combined with an equalizing pulse.
  • the invention comprises a circuit for combining these selected levels into an electrical signal having a stepped waveform and a circuit for further processing this signal to change its amplitude or remove undesired D.C. or frequency components.
  • the present invention further includes a conductive system for applying such a signal to the human body, animal body, isolated tissues or cell cultures, foods, beverages or other materials in order to relieve pain, stimulate healing, or devitalize selected pathogenic organisms which may be present.
  • Such “mimic” signals have been shown to have many effects in the body, including helping to direct mobile cells such as fibroblasts and macrophages to sites where they are needed (galvanotaxis) and causing the release of cell growth factors such as transforming growth factor beta (TGF- ⁇ ) and insulin-like growth factor (IGF).
  • TGF- ⁇ transforming growth factor beta
  • IGF insulin-like growth factor
  • the results can include more rapid healing of skin and muscle wounds, including chronic ulcers such as those resulting from diabetes, with minimal scarring; the mending of broken bones, including most nonunion fractures; the regrowth of injured or severed nerves; the repair of tissues damaged by repetitive motion, as in tendonitis and osteoarthritis; and the reduction of swelling, inflammation, and pain, including chronic pain for which the usual drug- based treatments do not bring satisfactory relief.
  • Some of the body's signals such as the "injury potential” or “current of injury” measured in wounds, are DC (direct current) only, changing slowly with time. It has been found that bone fracture repair and nerve regrowth are typically faster than usual in the vicinity of a negative electrode but slower near a positive one, where in some cases tissue atrophy or necrosis may occur. For this reason, most recent research has focused on higher-frequency, more complex signals often with no net DC component. While most complex-signal studies to date have been performed on bone fracture healing, the commonality of basic physiological processes in all tissues suggests that appropriate signals will be effective in accelerating many other healing and disease-recovery processes, although not all such signals will necessarily be alike.
  • FIG. 1 shows a schematic view of a waveform 20 which has been found effective in stimulating bone fracture healing, where a line 22 represents the waveform on a short time scale, a line 24 represents the same waveform on a longer time scale, levels 26 and 28 represent two different characteristic values of voltage or current, and intervals 30, 32, 34 and 36 represent the timing between specific transitions.
  • Levels 26 and 28 are usually selected so that, when averaged over a full cycle of the waveform, there is no net direct-current (D.C.) component.
  • waveform such as 20 is typically modified in that all voltages or currents decay exponentially toward some intermediate level between levels 26 and 28, with a decay time constant preferably longer than interval 34. The result is represented by a line 38.
  • interval 30 is about 200 microseconds, interval 32 about 30 microseconds, interval 34 about 5 milliseconds, and interval 36 about 60 milliseconds. Alternate repetition of intervals 30 and 32 generates pulse bursts 40, each of the length of interval 34, separated by intervals of length 36 in which the signal remains approximately at level 28.
  • Each waveform 38 thus consists of rectangular waves alternating between levels 26 and 28 at a frequency of about 4400 Hz and a duty cycle of about 85%.
  • the pulse bursts are repeated at a frequency of about 15 Hz and a duty cycle of about 7.5%, alternating with periods of substantially no signal.
  • tissues may respond differently to markedly different frequencies and waveforms.
  • the waveform of Figure 1 is effective in speeding the healing of a bone fracture but much less so in slowing the progress of osteoporosis.
  • a waveform 50 (Fig.
  • a peak effectiveness 62 typically falls somewhere between one and ten microamperes per square centimeter ( ⁇ A/cm ⁇ ), and a crossover point 64 at about a hundred times this value. Beyond point 64, the signal may slow healing or may itself cause further injury. Similar responses are seen in other biological processes that are responsive to electrical stimulation, including cell division, protein and DNA synthesis, gene expression, and intracellular second-messenger concentrations. For example, while conventional TENS can block pain perception with a relatively strong signal, much as a jamming signal blocks radio communication, it can also lead to progressively worsening injury since the pain's warning function has also been defeated.
  • Petrofsky U.S. No. 5,974,342 shows a microprocessor-controlled apparatus for treating injured tissue, tendon, or muscle by applying a therapeutic current.
  • the apparatus has several channels that provide biphasic constant voltage or current, including a 100-300 microsecond positive phase, a 200-750 microsecond inter-phase, and a 100-300 microsecond negative phase occurring once every 12.5-25 milliseconds. Pilla et al.
  • U.S. No. 5,723,001 disclose an apparatus for therapeutically treating human body tissue with pulsed radio-frequency electromagnetic radiation.
  • the apparatus generates bursts of pulses having a frequency of 1-100 MHz, with 100-100,000 pulses per burst, and a burst repetition rate of 0.01-1000 Hz.
  • the pulse envelope can be regular, irregular, or random.
  • Bartelt et al. U.S. 5,117,826) discloses an apparatus and method for combined nerve fiber and body tissue stimulation.
  • the apparatus generates biphasic pulse pairs for nerve fiber stimulation, and a net DC stimulus for body tissue treatment (provided by biphasic pulse trains having a greater number of negative than positive pulses).
  • biphasic pulse trains having a greater number of negative than positive pulses.
  • Bartelt, et al. describe a device for stimulating enhanced healing of soft tissue wounds that includes a plurality of signal generators for generating output pulses.
  • the intensity, polarity, and rate of the output pulses can be varied via a series of control knobs or switches on the front panel of the device.
  • Gu et al. (U.S. No. 5,018,524) show an apparatus that generates a pulse train made up of bursts having the same width, where each burst is made up of a plurality of pulses of a specific frequency.
  • the number of pulses varies from one burst to the next; the frequency of the pulses in each burst varies from one burst to the next corresponding to the variation in the number of pulses in each burst.
  • the pulses have a frequency of 230-280 KHz; the duty cycle of the bursts is between 0.33% and 5.0%.
  • Liss et al. (U.S. No. 5,109,847) relates to a portable, non-invasive electronic apparatus which generates a specifically contoured constant current and current-limited waveform including a carrier frequency with at least two low-frequency modulations.
  • the carrier frequency is between 1-100,000 KHz; square-wave or rectangular-wave modulating frequencies are 0.01-199 KHz and 0.1-100 KHz.
  • Borkan's tissue stimulator (U.S. No. 4,612,934) includes an implantable, subcutaneous receiver and implantable electrodes.
  • the receiver can be noninvasively programmed after implantation to stimulate different electrodes or change stimulation parameters (polarity and pulse parameters) in order to achieve the desired response; the programming data is transmitted in the form of a modulated signal on a carrier wave.
  • the programmed stimulus can be modified in response to measured physiological parameters and electrode impedance.
  • Hondeghem U.S. No.
  • Bastyr, et al. U.S. No. 5,487,759 disclose a battery-powered device that can be used with different types of support devices that hold the electrode pads in position.
  • Keyed connectors provide a binary code that is used to determine what type of support device is being used for impedance matching and carrier frequency adjustment.
  • the carrier frequency is about 2.5-3.0 KHz; the therapeutic frequency is typically on the order of 2-100 Hz.
  • Kolen U.S. No. 5,350,414) provides a device where the carrier pulse frequency, modulation pulse frequency, intensity, and frequency/amplitude modulation are controlled by a microprocessor.
  • the device includes a pulse modulation scheme where the carrier frequency is matched to the electrode-tissue load at the treatment site to provide more efficient energy transfer.
  • Liss et al. U.S. No. 4,784,142 discloses an electronic dental analgesia apparatus and method. The apparatus generates an output with relatively high frequency (12-20 KHz) pulses with nonsymmetrical low frequency (8-20 Hz) amplitude modulation.
  • Bartelt et al. U.S. No. 5,063,929) describe a microprocessor- controlled device that generates biphasic constant-current output pulses. The stimulus intensity can be varied by the user.
  • Charters et al. U.S. No.
  • 4,938,223) provide a device with an output signal consisting of bursts of stimuli with waxing and waning amplitudes, where the amplitude of each stimulus is a fixed percentage of the amplitude of the burst.
  • the signal is amplitude-modulated to help prevent the adaptation response in patients.
  • Molina-Negro et al. U.S. No. 4,541,432 disclose an electric nerve stimulation device for pain relief.
  • the device produces a bipolar rectangular signal with a preselected repetition rate and width for a first time period. Then, a rectangular signal is generated at a pseudo-random rate for a second time period, and delivery of the signal is inhibited for a third, pseudo-random period of time.
  • This protocol is said to substantially eliminate adaptation of nerve cells to the stimulation.
  • Butler et al. U.S. No. 4,431,000 show a transcutaneous nerve stimulator for treating aphasias and other neurologically-based speech and language impairments.
  • the device uses a pseudorandom pulse generator to produce an irregular pulse train composed of trapezoidal, monophasic pulses which mimic typical physiological wave forms (such as the brain alpha rhythm).
  • a series of such pulses has a zero DC level; a current source in the device reduces the effects of variables such as skin resistance.
  • Maurer U.S. No. 4,340,063 discloses a stimulation device which can be implanted or applied to the body surface.
  • the amplitude of the pulse decreases with a degradation in pulse width along a curve defined by a hyperbolic strength-duration curve. This is said to result in proportionately greater recruitment of nerve fibers due to the nonlinear relationship between pulse width and threshold.
  • the Kosugi, et al. system (U.S. No. 4,338,945) generates pulses that fluctuate in accordance with the 1/f rule. That is, the spectral density of the fluctuation varies inversely with the frequency: pleasant stimuli often have stochastic fluctuations governed by this rule. The system produces an irregular pulse train said to promote patient comfort during the stimulation.
  • Signal generators are also used in hearing prostheses. For example, McDermott's receiver/stimulator (U.S. No.
  • 4,947,844 generates a series of short spaced current pulses, with between-pulse intervals of zero current having a duration longer than that of each spaced pulse.
  • the waveform of the stimulus current includes a series of these spaced pulses of one polarity followed by an equal number of spaced pulses of opposite polarity so that the sum of electrical charge transferred through the electrodes is approximately zero.
  • Alloca U.S. No. 4,754,7590 describes a neural conduction accelerator for generating a train of "staircase-shaped" pulses whose peak negative amplitude is two-thirds of the peak positive amplitude.
  • the accelerator design is based on Fourier analysis of nerve action potentials; the output frequency can be varied between 1-1000 Hz.
  • Galbraith U.S. No.
  • 4,592,359 describes a multi-channel implantable neural stimulator wherein each data channel is adapted to carry information in monopolar, bipolar, or analog form.
  • the device includes charge balance switches designed to recover residual charge when the current sources are turned off (electrode damage and bone growth are said to be prevented by not passing DC current or charge).
  • electrotherapeutic treatment only grudgingly, and to date it is used only rarely. This seems to be a legacy from early beliefs that signals would need to have high local intensities to be effective.
  • Most electrotherapeutic apparatus now available relies either on direct implantation of electrodes or entire electronic packages, or on inductive coupling through the skin using coils which generate time-varying magnetic fields, thereby inducing weak eddy currents within body tissues.
  • the present invention comprises an apparatus and method for generating an electrical signal for use in biomedical applications.
  • the present invention provides devices and methods for alleviating a wide variety of health problems in both humans and animals.
  • the present invention enables the delivery of bioelectrical stimulation wherein the electrical signal closely mirrors natural body signals.
  • the receiving tissue is subject to minimal stress and healing is not only accelerated, but pain relief is also more permanent than that which takes places with other devices.
  • the apparatus according to the invention may be used to provide electrotherapeutic treatment for human and animal patients, including, but not limited to, healing acceleration (bone and soft tissue), relief of acute or chronic pain, and relief of swelling and/or inflammation.
  • Isolated skin cells for example, might be treated with chosen waveforms in an appropriate medium to increase cell proliferation and differentiation in the preparation of tissue-cultured, autogenous skin-graft material.
  • the growth of bacteria genetically engineered to produce a desirable product, such as human insulin might be accelerated, or their secretion of the desired product increased, by treatment with a suitable waveform.
  • the apparatus of the present invention may be used to provide in vivo, customizable electrotherapeutic treatment for human and animal patients, including but not limited to healing acceleration, relief of acute or chronic pain, and relief of swelling and/or inflammation. Since isolated cells or tissue cultures can also be affected by electrotherapeutic waveforms (appropriate electrical stimuli have been observed to modify the rates of cell metabolism, secretion, and replication), the apparatus may also be used for in vitro applications. In contrast to TENS-type devices, which are aimed at blocking pain impulses in the nervous system, the apparatus operates at a signal level which is below the normal human threshold level of sensation and pain: most users do not experience any sensation during treatment, apart from a steady decrease in previously existing pain.
  • An apparatus for generating an electrical signal includes means for generating primary timing intervals and secondary timing intervals into which at least one primary timing interval is divided. Embodiments of this aspect may include that the primary timing intervals form a charge balanced primary cycle. Accordingly, it is an object of the present invention to provide an apparatus and method for treating a wide variety of physiological symptoms by administering novel pulsed electrical signals to the body. It is another object of the present invention to provide an apparatus and method for accelerating the healing of wounds. It is another object of the present invention to provide an apparatus and method for reducing tissue swelling. Another object of the present invention is to provide an apparatus and method for increasing angiogenesis. It is yet another object of the present invention to provide an apparatus and method for improving the survival of skin grafts.
  • FIG. 1 is a schematic view of a waveform used in stimulating bone fracture healing.
  • Fig. 2 illustrates a waveform used in the treatment of osteoporosis.
  • Fig. 3 is a schematic view of healing effect vs. signal intensity (amplitude).
  • Fig. 4 illustrates a waveform according to the invention, having a carrier frequency contained within a pulsed envelope.
  • Fig. 5 illustrates a generalized waveform according to the invention, having a series of primary timing intervals and signal amplitudes contained within a stepped envelope approximating an arbitrary curvilinear function.
  • Fig. 1 is a schematic view of a waveform used in stimulating bone fracture healing.
  • Fig. 2 illustrates a waveform used in the treatment of osteoporosis.
  • Fig. 3 is a schematic view of healing effect vs. signal intensity (amplitude).
  • Fig. 4 illustrates a waveform according to the invention, having a carrier frequency contained within a pulsed envelope.
  • FIG. 6 illustrates a waveform according to the invention, having a carrier frequency contained within an approximately sinusoidal envelope.
  • Fig's. 7-9 illustrate waveforms according to the invention, also having carrier frequencies contained within approximately sinusoidal envelopes, but demonstrating alternative modulation schemes.
  • Fig. 10 illustrates a waveform according to the invention, having a carrier frequency contained within an irregularly pulsed envelope;
  • Fig. 11 illustrates a waveform according to the invention, having a carrier frequency contained within an envelope which approximates exponential decay.
  • Fig. 12 illustrates a waveform according to the invention, having two different carrier frequencies contained within alternate pulses of a pulsed envelope.
  • Fig. 13 illustrates a simplified version of the waveform in Fig. 4.
  • Fig. 14 illustrates a still more simplified version of the same waveform.
  • Fig. 15 illustrates a waveform built up from successive pulses like that in Fig. 13, but with alternating polarities.
  • Fig. 16 illustrates a waveform representing that in Fig. 6 after a typical combination of low-pass filtering and D.C. blocking.
  • Fig. 17 illustrates a method for applying waveforms, such as those shown in the preceding Figures, to the human body or a portion thereof, using conductive electrodes.
  • Fig. 18 illustrates a method for applying waveforms, such as those shown in the preceding Figures, to the human body or a portion thereof, using conductive electrodes, in conjunction with an external fixator for the purpose of bone lengthening.
  • FIG. 19 illustrates a method for applying waveforms, such as those shown in the preceding Figures, to the human body, a portion thereof, or another material, using a bath of conductive liquid.
  • Fig. 20 illustrates a method for applying waveforms, such as those shown in the preceding Figures, to the human body or a portion thereof, using conductive electrodes and a conductive dressing, for the purpose of wound healing.
  • Fig. 21 illustrates a generalized electronic configuration of the invention, using discrete integrated-circuit timers and sequencers.
  • Fig. 22 illustrates a generalized electronic configuration of the invention, using a microcontroller or microprocessor.
  • Fig. 23 illustrates a simplified circuit which, for purposes of illustration, generates a waveform similar to that in Fig. 4.
  • Fig. 24 illustrates a second specific embodiment of the invention, configured to generate a waveform similar to that in Fig. 6 or Fig. 16.
  • Fig. 25 illustrates waveforms associated with the circuit in Fig. 24.
  • Fig. 26 illustrates a third specific embodiment of the invention, configured to provide a choice of waveforms of types broadly similar to those in Fig. 4, Fig. 6 or Fig. 10.
  • Fig. 27 illustrates waveforms associated with the circuit in Fig. 26.
  • Fig. 28 illustrates a fourth specific embodiment of the invention, configured to generate a waveform similar to that in Fig. 12 but also incorporating polarity reversal.
  • Fig. 29 illustrates waveforms associated with the circuit in Fig. 28.
  • FIG. 30 illustrates an exponential decay curve and various signal types having envelopes which decay approximately exponentially.
  • Fig. 31 illustrates a fifth specific embodiment of the invention, configured to generate a waveform similar to the bottom one in Fig. 30.
  • Fig. 32 illustrates waveforms associated with the circuit in Fig. 31.
  • Fig. 33 illustrates a sixth specific embodiment of the invention, also configured to generate a waveform similar to the bottom one in Fig. 30 but with greater precision and reproducibility.
  • Fig. 34 illustrates waveforms associated with the circuit in Fig. 33.
  • the following description includes the best presently contemplated mode of carrying out the invention. This description is made for the purpose of illustrating the general principles of the inventions and should not be taken in a limiting sense.
  • the entire text of the references mentioned herein are hereby incorporated in their entireties by reference, including United States Provisional Application Serial No. 60/480,890.
  • the present invention overcomes the shortcomings of prior art devices by enabling the delivery of bioelectrical signals optimized to correspond to natural body signals resulting in accelerated and more permanent healing.
  • the signals described herein uniquely conform to natural signals and consequently tissues subjected to electrostimulation according to the present invention undergo less physiological stress when compared to electrostimulation from previous devices.
  • the present invention is non-invasive and cost-effective making it desirable for multiple applications for persona] and individual use.
  • the signal includes a waveform consisting of intermittent bursts of quasi-rectangular waves (waves of generally rectangular shape but typically somewhat distorted), based on a plurality of relatively long primary timing intervals Ti, T 2 and so forth, forming in succession a primary repeating cycle; a plurality of shorter secondary timing intervals tj, t 2 and so forth, into which at least one of said primary intervals is divided, and forming in succession a secondary repeating cycle which continues throughout the length of that primary interval, while at least one other of said primary intervals is not so divided; and a plurality of constant voltage or current levels Li, L 2 and so forth, one of which is selected during each primary timing interval or, if that interval is divided, during each secondary timing interval within it.
  • the series of constant current or voltage levels which are selected during successive timing intervals comprises the waveform; the average magnitude of these levels selected during a given primary interval determines the signal amplitude within that interval; and the signal amplitudes within all primary intervals, taken in succession, comprise the envelope of the waveform.
  • the apparatus includes a first timing block for generating primary timing intervals Tj, T 2 and so forth; a second timing block for generating secondary timing intervals t ls t 2 and so forth; an interconnection block for combining these intervals into an output signal having predetermined relationships among the intervals; an output block for transmitting the output signal to a load (such as tissue being treated with the apparatus); a battery pack; and, optionally, a filter for removing unwanted frequency components from the output signal; and an adjustment block for chosing from among a plurality of output signals with predetermined characteristics.
  • the first and second timing blocks may run either asynchronously or synchronously, and in the latter case, either the first timing block may be driven by the second, producing primary timing intervals Tl, T2- T3, T4 5 and also T5, and T6 and so forth if present by frequency division, or both timing blocks may be driven in a like manner by a shared timing source such as a crystal-controlled oscillator.
  • Tl will be considered to be the "at least one" primary timing interval which is not divided into a plurality of shorter secondary timing intervals; Ll the constant level of voltage or current which is maintained during Tl ; and T2 the "at least one" primary timing interval which is so subdivided.
  • Subsequent primary timing intervals T3, T4 and others if present and so forth may be so subdivided or not, as set forth in each individual example.
  • the signal has a first amplitude level Ll throughout primary interval Tl, then assumes a plurality of levels L2, L3 and so forth (which may also, optionally, include Ll) in succession during the secondary cycle formed by intervals tl, t2 and so forth into which T2 is subdivided.
  • the following primary intervals T3, T4 and others if present and so forth, if present, may each then either contain a secondary cycle in the manner of T2, or not, in the manner of Tl.
  • the term “select” and variations thereof are intended to refer to a range of options under circuit control.
  • the term “chose” and variations thereof are intended to refer to a range of options under direct human control.
  • the secondary cycle in such a composite waveform may be considered as a carrier wave, and the primary cycle as a signal which modulates the carrier wave with a specified, repeating envelope.
  • two primary intervals contain secondary cycles running at different rates, these may be considered as two different carrier frequencies.
  • An important feature of the invention is that its output appears as a floating, differential voltage or limited current between one pair (or, optionally, as such voltages or currents between several such pairs) of output pins or other connectors.
  • the output signals may thus be coupled to the body through simple skin-contact electrodes, through conductive wound dressings, through conductive devices (such as metal bone fixation pins or electrically-conductive catheters) which have already been implanted for other purposes, through bodies of conductive liquid in contact with the skin or other tissues, or by similar conductive means, providing a wide range of flexibility to suit individual cases.
  • An apparatus according to the invention is lightweight, compact, self-contained, cost-effective to manufacture and maintain, and convenient to carry or wear for extended periods. It is safe for unsupervised home use without the need for special training, and able to generate a signal as described above and deliver it efficiently to the body. Since only low voltages and currents are used, the apparatus does not pose a shock hazard even in case of malfunction power may be furnished by compact and inexpensive batteries, typically needing replacement only once in several weeks of use.
  • the output signal is an important feature of the present invention.
  • the output signal is a waveform based on at least two, but optionally a greater number, of relatively long primary timing intervals Tl, T2, T3, T4 5 and also T5, and T and so forth, forming in succession a primary repeating cycle; at least two, but optionally a greater number, of shorter secondary timing intervals tl, t2 and so forth, into which at least one of said primary intervals is divided, and forming in succession a secondary repeating cycle which continues throughout the length of that primary interval; and a plurality of constant voltage or current levels Ll, L2 and so forth, one of which is presented to the output during each primary timing interval or, if that interval contains a secondary cycle, during each secondary timing interval within it.
  • the resulting stepped waveform may then be passed through any of various types of active or passive filter in order to emphasize or attenuate chosen frequency ranges.
  • the primary cycle may be either periodic (automatically repeating at fixed intervals) or aperiodic (repeating only in response to some outside event).
  • the relative lengths of primary intervals Tl, T2 and so forth may differ, but each is fixed in length from one primary cycle to the next.
  • all primary intervals are fixed in length with the exception of Tl, which may be arbitrarily long.
  • Timing intervals Tl, T2 and so forth, and tl, t2 and so forth have the following relationships:
  • each primary interval T l5 T 2 and so forth may have any length from 50 microseconds to 30 seconds, while their sum (one complete primary cycle) may have any length from 200 microseconds to 120 seconds; each secondary interval tl, t2 and so forth may have any length from 2.5 microseconds to 50 milliseconds, while the sum of (t a + tb + ...) (one complete secondary cycle) may have any length from 5 microseconds to one-half of the primary interval during which the secondary cycle appears; and "stray" secondary intervals at the start or end of a primary interval may be present so long as their total does not exceed two secondary cycle lengths.
  • the primary cycle is aperiodic, conditions (a) and (b) are modified to
  • (T 2 , T 3 , ...) indicates any one of primary intervals T 2 , T 3 and so forth, and (T2 + T3 + 7) indicates the sum of these intervals, equal to the length of a primary cycle excluding Tl which, as stated above, may be arbitrarily long. All other relationships are the same as above. Where two or more primary intervals are spent at constant output levels, these levels need not be the same, and where two or more primary intervals contain secondary cycles, the intervals and corresponding output levels within them need not be identical. While the effect of (d) is to ensure that at least two complete secondary cycles will appear during any primary interval which contains them, in practice the number may range upward to several hundred or even a few thousand.
  • an effect of (e) is that one or more of the secondary intervals may be unusually long, short, or even missing during the first or last secondary cycle, or both, within a given primary interval. All secondary cycles apart from the first and the last, however, contain all of the specified intervals with each having substantially its specified length. Most often, missing or drastically shortened intervals occur when the primary and secondary cycles run asynchronously, so that a primary transition may occur at any time within the secondary cycle and thus any primary interval TA may or may not include an integral number of secondary cycles.
  • a primary interval TA might contain either "ta, b, tc, td, ta, tb, tc, td, ta, tb, tc, td" (three complete secondary cycles), or "ta, b, c, td, t a , t , t c , td, ta, tb, ty" (two complete cycles, plus a third one cut off partway through, with ty representing a shortened tc).
  • the first secondary interval within a primary interval may also appear abnormally long or short when the secondary frequency generator is restarted after a primary interval in which it has been disabled.
  • a frequency generator constructed as shown in Figures 23, 24, and 28 such a distorted interval will typically be about one-fourth longer than normal, while with a generator constructed as in Figure 31, it will be about one-third shorter than normal.
  • a two-stage secondary cycle might begin "tx, tb, ta, tb, t a , tb-" where t x represents a t lengthened or shortened by startup transients.
  • any such distorted intervals or portions of incomplete cycles are regarded as "strays" for the purposes of (e), and within a given primary cycle will total not more than twice the secondary cycle length.
  • the intervals making up any given primary cycle may all be nominally equal, or not.
  • Constant voltage or current levels Ll, L2 and so forth are typically generated first as differential voltage levels, which may thereafter be translated into levels of current. Preferably, to conserve battery power, such translation into current takes place only after the selection of a voltage level for each timing interval, so that non-selected levels during each such timing period consume no current.
  • all voltages within the apparatus lie within the range between -42.4 volts and +42.4 volts, thereby meeting the IEC 950 definition of "safety ultra-low voltages.”
  • any output currents preferably lie within the range between -10.0 milliamperes and +10.0 milliamperes, as prescribed by ANSI/AAMI NS4-1985 for safe application to the human body.
  • Ll may be either the most positive voltage appearing at any time in the primary cycle, the most negative such voltage, or any voltage intermediate between these limits. In the latter case, Ll preferably lies midway between these limits and represents zero voltage or current.
  • L2, L3, and so forth (as many as applicable) will be the levels which appear in the secondary cycle within T2- Note that Ll may also be present in this cycle. Levels which first appear in any following primary or secondary intervals will be numbered consecutively in the same manner. In most cases, only three levels Li, L2 and L3 are required.
  • a basic waveform is generally described in U.S. Patent #6,535,767, incorporated herein by reference, and is shown in Figure 4.
  • the waveform includes three primary intervals Tl, T2 and T3, indicated respectively by characters 80, 82 and 84, and three output levels Ll, L2 and L3, indicated respectively by characters 90, 92 and 94.
  • a secondary cycle appears within T2.
  • the secondary intervals are not individually labeled and, for purposes of illustration, an atypically small number of secondary cycles is shown.
  • the flow of time is from left to right, with vertical bars 96a and 96b representing the start of Tl in each of two successive cycles, so that the interval between them represents one full cycle.
  • Solid line 98 indicates the output, which is held constant at level Ll during Tl; undergoes a secondary cycle during T2, in which it alternates between level L2 during tl and L3 during t2; and again is held constant during T3, but at L3 rather than at Ll. At the end of T3, the cycle begins again with Tl and the output changes again to a constant Ll. Further details of this waveform, means of generating it, and some of its potential uses, may be found in U.S. Patent #6,535,767.
  • the present invention extends this three-stage waveform to a primary cycle consisting of four or more primary timing intervals Tl, T2, T3, T4 and others if present, as generally indicated by arrows 100 in Figure 5, forming in succession a repeating primary cycle; at least two relatively shorter secondary timing intervals tl, t2 and so forth, into which at least one such primary timing interval is divided and which form in succession a repeating secondary cycle throughout its length, while at least one other primary timing interval is not so divided; a plurality of substantially constant voltage or current levels Ll, L2 and so forth, one of which is selected during each secondary interval within a primary interval which is so divided, or during the whole of a primary interval if it is not so divided; a resulting range of possible signal amplitude levels, generally indicated by 102; and an envelope 104 consisting of rectangular steps, one for each primary timing interval.
  • Each signal amplitude consists of both an A.C. (time- variant) and
  • D.C. time-invariant component
  • the D.C. amplitude is most conveniently expressed as the time average of the voltage or current within the respective primary timing interval, and the A.C. amplitude, as the root mean square (RMS) value of the instantaneous difference of the voltage or current from this average:
  • D is the D.C. component
  • TA is a given primary timing interval
  • Q(t) is the voltage or current during that interval as a function of time
  • A is the A.C. (RMS) component
  • 'Tnt(TA) ••• dt represents an integral with respect to time taken throughout the length of TA
  • Sqr indicates the square root function.
  • a nonzero A.C. amplitude during any primary timing interval results from the presence of a secondary cycle. Vertical hatching within steps of envelope 104 is not meant to indicate any particular timing within such a secondary cycle, but merely that such a cycle is present within those steps, resulting in a nonzero A.C. amplitude.
  • the voltage or current maintains a uniform value throughout, and as a result the A.C.
  • envelope 104 may be caused to emulate any periodically or aperiodically repeating real-world mathematical function, as suggested by the arbitrary, curvilinear envelope 106.
  • Examples of real- world envelopes whose emulation is within the scope of the invention are sinusoidal "interferential" envelope 108, decaying exponential envelope 110, symmetrical repeating pulse- train envelope 112, asymmetrical repeating pulse-train envelope 114 with alternate polarity reversal, and asymmetrical repeating pulse-train envelope 116 with charge-equalizing interval 118.
  • This last example is equivalent to the waveform already shown in Figure 4 and discussed in the accompanying text.
  • Another feature of the present invention is the filter, which optionally blocks frequencies above a chosen level to create a desired transition profile or to prevent interference by external high-frequency signal sources.
  • the filter may include a shunt capacitance, a resistor network, a voltage- controlled current source, or other suitable device that simultaneously slows and controls the rate of transitions, attenuates output frequency components above about 10 F m ax (or other selected frequency), and prevents interference with circuit functioning by external radio- frequency signals.
  • the filter may block D.C. components from the output, provide voltage step-up through a transformer, or both.
  • Yet another feature of the present invention is the use of dual timing blocks, each optionally incorporating a multistep sequencer, to generate waveforms that can be combined to produce an output waveform having selected characteristics.
  • one of the timing blocks is controlled by the sequencer and the sequencer is driven by the other timing block: that is, the output of the block which generates secondary timing intervals tl, t2 and so forth may be "on,” “off,” or have different timing characteristics, depending on the output state of the sequencer.
  • Such different timing characteristics may be produced, for example, by incorporating a plurality of alternative component values into the second timing block, with each one switched either into or out of the circuit depending upon the sequencer outputs. This results in a circuit that generates an output signal whose characteristics — frequency, duty cycle, amplitude — can be determined over a wide range by the particular chosing of components and the way in which they are interconnected, with a surprisingly simple overall circuit configuration.
  • Another feature of the present invention is the use of conventional, readily-available low-voltage batteries as a safe and convenient power source for the apparatus. While the invention may be used with AC (alternating current) power sources (with the addition of any suitable adapter), battery power is preferred since it not only reduces the size and weight of the apparatus, but also adds to its safety and ease of use for a patient undergoing treatment. Typically, the batteries need to be replaced at infrequent intervals (generally no more than once every few weeks, depending on the output signal and the particular application), simplifying patient compliance and reducing operating costs. Only low power levels, such as are required to produce therapeutic effects, are applied to the body. Thus, the invention cannot produce an electrical shock hazard even in the event of a malfunction, and is therefore suitable for unsupervised home use.
  • Still another feature of the present invention is its versatility.
  • the apparatus may be configured easily so as to produce an output waveform with choosable timing intervals, output voltage or current levels, and overall envelope, or to allow choice among a plurality of any of these, to address various physiological needs.
  • tissues may respond in different ways to different signal frequencies, to a pure AC signal, or to an AC signal with a superimposed positive or negative DC component.
  • different effects may appear at different current densities.
  • An apparatus with an adjustable output signal is useful for a greater variety of applications than one having a fixed output.
  • medical professionals may prefer a generator having a fixed output, or an output that is adjustable only in magnitude, for outpatient use by their patients.
  • Embodiments of the invention are described in which the user can adjust the frequency of a signal for a given application by turning a rotary switch or other means to chose one of a plurality of the available signals noted above, while other described embodiments are not so adjustable.
  • Yet another feature of the invention is its versatility in means of application. Signals generated by the circuitry of the invention are easily applied to the human or animal body, to living tissue or cell cultures, or to foodstuffs or pharmaceutical materials, by a variety of different, either invasive or noninvasive, electrically-conductive means.
  • reference numerals are used to identify structural elements, portions of elements, surfaces or areas in the drawings, as such elements, portions, surfaces or areas may be further described or explained by the entire written specification.
  • the objective of the invention is to generate any one or any combination of a broad class of waveforms, for use in biomedical applications, each of which is based on a plurality of relatively long primary timing intervals Tl, T2 and so forth, forming in succession a primary repeating cycle; a plurality of shorter secondary timing intervals tl, t2 and so forth, into which at least one of said primary intervals is divided, and forming in succession a secondary repeating cycle which continues throughout the length of that primary interval, while at least one other of said primary intervals is not so divided; and a plurality of constant voltage or current levels Ll, L2 and so forth, one of which is presented to the output during each primary timing interval or, if that interval contains a secondary cycle, during each secondary timing interval within it.
  • stepped waveform may then be passed through any of various types of active or passive filter in order to emphasize or attenuate chosen frequency ranges.
  • active or passive filter As was previously shown in Figure 5, by following the principles of the present invention, a waveform having an envelope consisting of a sufficient number of rectangular steps can be tailored to approximate virtually any curvilinear function. Many such functions are characteristic of real-world applications.
  • Typical examples of such real-world functions are the sinusoidal envelope which is produced when two sine waves at similar frequencies and amplitudes interfere, alternately reinforcing each other and canceling each other out; and the exponential envelope which is produced when an oscillatory system, such as a plucked harp string, radiates away energy progressively so that the amplitude of its oscillations decreases smoothly over time.
  • an oscillatory system such as a plucked harp string
  • carrier frequencies typically range from about 1000 to about 10,000 Hz, with frequencies between 4000 and 4500 Hz most common although for some applications higher frequencies, up to approximately 200 KHz, may be preferable.
  • Beat frequencies differ widely for various conditions, but typically lie in the range from 1 Hz to 500 Hz.
  • a first approximately sinusoidal waveform following the principles of the invention, consists of five primary timing intervals Tl- T5, of which Tl and T5 are spent at constant output levels Ll and L3 respectively, T5 thereby serving as an equalizing pulse, while T2, T3 and T4 all contain secondary cycles. Where charge balance is established by other means, an equalizing pulse may not be needed and in such a case, T5 may be omitted.
  • the secondary cycles within T2 and T4 are alike in timing and A.C. amplitude, while that in T3 has a higher A.C. amplitude than those in T2.
  • the A.C. amplitude within T3 is about twice that in T2 or T4. More preferably, T2 and T4 are each shorter than T3.
  • T2 and T4 are each about twice the combined length of Tl and T5, while T3 is about three times the combined length of Tl and Y5.
  • An advantage of this specific combination of timing intervals is that it approximates the sinusoidal envelope with minimum numbers of primary intervals and of discrete voltage or current levels, thus permitting great potential circuit simplicity and efficiency.
  • a representative example of this five-stage (or four-stage, if T5 is omitted), quasi-sinusoidal or "interferential-like" waveform, using only three voltage or current levels Ll, L2 and L3, is shown in Figure 6.
  • the repetition rate of the primary cycle represents the beat frequency
  • the repetition rate of the secondary cycle represents the carrier frequency.
  • Amplitude reduction during T2 and T4, relative to T3, is achieved by keeping the same timing, but switching between more closely-spaced voltage or current levels.
  • the secondary cycle within T4 is shown with a different D.C. offset from that in T2.
  • Figure 6 and all others following it which depict waveforms (Figures 7 through 16, 25, 27, 29, 30, 32 and 34) follow the same conventions which were used in Figure 4, but with the following simplifications: (1) A single primary cycle is shown in each Figure, beginning with Tl at the left margin of the figure, and ending at the right margin. (2) Dashed lines indicating Ll, L2 and so forth are omitted except where cited in the text, since these levels are clearly shown by the flat tops and bottoms of the pulses in each Figure.
  • the lower- amplitude or "step-in” and “step-out” periods corresponding to intervals 82a and 82c in Figure 6, now each exceed in length the "quiet" or "no- signal” period corresponding to interval 80.
  • the "quiet,” “step-in,” “full signal” and “step-out” periods have durations in the ratio 1 :2:3:2.
  • the result is a ratio of peak to average voltage or current (1.60) which closely approximates that of a mathematically pure sinusoid (1.57), and a ratio of peak to R.M.S. voltage or current (1.414) which is identical with the pure sinusoid's.
  • FIG. 8 Yet another representative four-stage, quasi-sinusoidal waveform is shown in Figure 8. This differs from the previous examples in that the higher average amplitude during T3 is achieved by switching between additional, higher voltage or current levels than those used in T2 and T4. Additional waveforms according to the invention may contain any integral number of primary intervals, and within each of them (except for the first) a secondary cycle containing any integral number of secondary intervals. For example, a more accurate emulation of sinusoidal energy distribution over time might be achieved using a larger number of primary timing intervals: either by selecting from among more than three constant voltage or current levels, by using varying duty cycles within the secondary cycles, or by a combination of these approaches, as shown in Figure 9.
  • such a waveform consists of an even number P of primary timing intervals Tl, T2, T3 and so forth, an even number S of secondary timing intervals tl, t2, t3 and so forth, and an odd number Q of voltage or current levels Ll, L2, L3 and so forth.
  • Voltage or current level Ll approximates zero voltage or current, while the remaining levels L2, L3 and so forth form pairs, each pair having roughly equal magnitudes but opposite polarities.
  • the members of such a pair may be represented by Lx and Ly, respectively. There may either be one such pair, as shown in Figures 6 and 7, or more than one pair, as shown in Figures 8 and 9. The use of a more widely-spaced pair yields a greater signal amplitude.
  • S may be any even integer, but is preferably four, yielding secondary timing intervals tl, t2, t3 and t4.
  • Intervals tl and 13 are preferably equal, as are t2 and t4, but the value of tl and t3 need not be the same as that of t2 and t4.
  • An increase in the duty cycle yields a greater signal amplitude.
  • Signal amplitudes may be selected by changing the combination of signal levels Ll, L2 and so forth which alternate during the secondary cycle, by changing the duty cycle of their alternation, or by a combination of these means, while both timing intervals and signal amplitudes are chosen to approximate a sinusoidal envelope, as shown in Figure 9.
  • the examples given above should not be interpreted as restricting the scope of the invention to signals of quasi-sinusoidal form, since it is an object of the invention to provide a maximum range of possible output signals, achievable by like means and using like circuitry, but not all necessarily having similar envelopes.
  • a non-sinusoidal envelope is shown in Figure 4.
  • Non-sinusoidal signals might find use in muscle stimulation or re-education, in which trains of short, high- intensity pulses must alternate with rest periods, causing alternate contraction and relaxation of the muscle fibers. It is well-known that different muscle fibers, and the nerves supplying them, have different response thresholds and thus respond best to impulses or bursts with different energies.
  • a waveform whose primary cycle includes several different burst lengths, with similarly varied intervals between them, may thus be more effective than one with only a single burst length and interval.
  • Figure 10 shows an example of such a waveform, employing ten primary intervals of which five contain identical secondary cycles but vary in length.
  • Non-sinusoidal signal is a pulsed signal which rises quickly to a maximum intensity, then decays in a linear, exponential or other fashion with time.
  • a six-stage waveform approximating such an exponential decay characteristic, using variable timing intervals within the secondary cycle to achieve the intensity variation, is shown in Figure 11.
  • the signal may be either periodic (automatically repeating) or aperiodic (occurring only when triggered by some external event, such as the press of a button).
  • the primary cycle might be initiated at the moment when electrodes make adequate contact with a body of food, beverage or pharmaceutical material to be treated.
  • Tl may be arbitrarily long.
  • FIG. 12 Yet another example of a non-sinusoidal signal is _ the one shown in Figure 12. This is simply a doubled version of the waveform which was shown in Figure 4, except that T2 and T5 now contain different secondary cycles representing different carrier frequencies.
  • a waveform of this type might be used in pain relief by alternately stimulating two known, pain- relieving biochemical channels which respond optimally at different frequencies.
  • stimulation around 2 to 4 Hz has been shown to produce long-lasting analgesia, but with a slow onset; stimulation around 100 to 200 Hz produces short-acting analgesia with a fast onset; while an alternation of both types of stimulation, each lasting for several seconds, activates both mechanisms so that the analgesia has a fast onset but long duration.
  • a waveform of the general type described above and according to the principles of the present invention will inherently be charge-balanced ⁇ that is, the output will show a net zero direct- current content « if the time average of positive and negative voltages or currents at the output, over the length of one primary cycle, is zero. This may be achieved in any of several ways.
  • the output may be passed through an output network which blocks direct current.
  • the positive and negative signal intervals may be balanced so that approximately equal amounts of time are spent in each state, minimizing the direct- current content.
  • the difference between tl and t2 during T2 introduces the desired charge imbalance. Note that this is simply the waveform which was previously shown in Figure 4, but here with its charge-balancing interval T3 removed.
  • the waveform may be deliberately unbalanced by making the polarities asymmetrical around zero: most simply, by eliminating all levels of a given polarity (positive or negative) as shown in Figure 14, where as before 120 represents a level Ll of zero voltage or current, 122 a positive level L2, but there is now no negative level L3.
  • FIG. 15 illustrates such a primary cycle, in which Tl and T3 represent intervals of zero voltage or current while T2 and T4 are intervals of charge-unbalanced signals.
  • T2 and T4 are equal in length, and equal and opposite in polarity, so that over the full primary cycle the charge remains balanced.
  • T2 and T4 are each preferably between 10 and 60 minutes in length, while Tl and T3 may each be substantially shorter.
  • any such waveform may then optionally be passed through a network of active or passive components, such as a resistor- capacitor network or operational-amplifier bandpass filter to attenuate selected frequency components, a transformer (with suitable driving circuitry) to step up the output voltage or provide isolation against possible leakage currents, or series capacitors to block direct current from the output.
  • a network of active or passive components such as a resistor- capacitor network or operational-amplifier bandpass filter to attenuate selected frequency components, a transformer (with suitable driving circuitry) to step up the output voltage or provide isolation against possible leakage currents, or series capacitors to block direct current from the output.
  • Figure 16 represents the waveform of Figure 7 after passage through a filter designed to block both direct current and frequency components higher than a few times F m ax-
  • T2 and so forth secondary intervals tl, t2 and so forth, or voltage/current levels Ll, L2 and so forth, either during treatment or between successive treatments.
  • tl, t2 and so forth may be adjusted, preferably together so that the ratio between them is preserved, creating different carrier frequencies to compensate for variable user skin impedance, while Tl, T2 and so forth may be adjusted, again preferably together, to change the effective beat frequency thus activating different tissue repair processes.
  • the spans between the applied voltages or currents Ll, L2 and so forth may be varied so as to compensate for variable tissue cross- sections under treatment or differing optimal current densities of various tissues.
  • Conditions believed to be treatable with waveforms include, but are not necessarily limited to, the following: bone fractures, osteoporosis, acute pain, chronic pain, swelling, simple inflammation, and inflammatory disorders such as tendonitis (including carpal tunnel syndrome and other repetitive stress injuries) and osteoarthritis. Accelerated healing of wounds, involving a variety of tissue types and resulting either from trauma or from degenerative conditions such as diabetes, may also be seen during treatment. However, it should be understood that no one set of timing intervals and voltage or current levels are useful for treating all (or even most) of these conditions.
  • the primary intent of the invention is to provide electrotherapeutic treatment for human and animal patients, including but not limited to healing acceleration, relief of acute or chronic pain, and relief of swelling and/or inflammation.
  • the apparatus need not be confined to use with intact organisms, since isolated cells or tissue cultures can also be affected by electrotherapeutic waveforms; appropriate electrical stimuli have been observed to modify the rates of cell metabolism, secretion, and replication.
  • Isolated skin cells might be treated with chosen waveforms in an appropriate medium to increase cell proliferation and differentiation in the preparation of tissue-cultured, autogenous skin-graft material.
  • the growth of bacteria genetically engineered to produce a desirable product, such as human insulin might be accelerated, or their secretion of the desired product increased, by treatment with a suitable waveform.
  • the viability of chosen organisms within a food product, beverage, drinking water or a pharmaceutical product might be decreased by similar treatment, again using a waveform chosen for the purpose.
  • the means of application is another important feature of the invention.
  • the broad range of achievable therapeutic signal waveforms, frequencies and strengths suits the invention to a broad range of such application means, including, but not necessarily limited to: conductive skin-contact electrodes; conductive wound dressings, such as hydrogels or saline-soaked gauze; conductive liquids, such as saline baths in which the body or any parts of it may be immersed; conductive materials, such as bone-fixation pins or catheters, which may have been inserted into or implanted in the body for other purposes; and conductive materials of like nature placed in contact with cell or tissue cultures, foodstuffs, drinking water and other beverages, or pharmaceutical materials.
  • Conductive as used in the preceding paragraph may refer to any one or combination of the following phenomena: metallic conduction; semiconductor-type conduction by either positive or negative charge carriers; primarily tunneling conduction, such as takes place in some carbon-filled plastics; ionic conduction, for example by the motion of ions in salt water or another, typically aqueous solution; electrolytic conduction, in which ions are oxidized or reduced at an interface, for example that between a metallic conductor and an ionic solution; and capacitive conduction, in which charge is transferred by displacement currents, for example through a thin sheet of insulating material, upon changes in the applied voltage.
  • FIG 17 illustrates a mode of use of the invention in which a stimulating signal is applied through a volume of body tissue 130 by means of conventional skin-contact electrodes 132a and 132b, such as those used in TENS (transcutaneous electric nerve stimulation).
  • TENS electrodes are inexpensive, widely available in a variety of shapes and styles, and usually self-adhesive.
  • they are placed on the skin 134 and driven by a signal source 136 in such a way that the current flowing between them includes the tissue volume to be treated.
  • the current will distribute itself primarily within a roughly football-shaped volume 138, lying within tissue volume 130 with one of its ends at each electrode. Tissues within volume 138 will therefore receive the most effective treatment.
  • FIG. 18 illustrates a specific application of the invention to a mode of therapy in which it is desired to stimulate bone growth for the purpose of bone lengthening.
  • the bone 150 is cut or broken, and each portion 150a or 150b is then fixed, using sets of rigid pins 152a or 152b, to a generally ring-shaped collar 154a or 154b respectively.
  • the gap between portions 150a and 150b is shown much wider than it would be in actuality.
  • Collars 154a and 154b are connected by extendable means 160, such as threaded rods joined by rotatable threaded sleeves. Pins, collars and connection means alike are commonly made chiefly from metals such as stainless steel.
  • extendable means 160 By progressively extending means 160 as new bone forms within the gap 162, the overall length of bone 150 is slowly increased. All too often, however, this method fails or is drastically slowed because bone does not fill the gap as quickly as desired, or because the new bone does not adequately calcify. The result can be either a permanent bone nonunion, or a porous bone which is at severe risk for re-breakage.
  • the invention adds electrostimulation for bone regrowth.
  • Conductive skin-contact electrodes 164a and 164b connected with a signal source 166 made according to the principles of the invention, are placed in such a way that the current flowing between them will include the tissue volume 166 surrounding and including the gap in the bone, but lies clear of pins 152a and 152b since a portion of the applied current could then flow through these pins, the collars and the connection means, rather than through tissue, and thus be wasted.
  • a waveform such as that of Figure 4, which is known to stimulate bone growth, is then applied from source 166 through the electrodes, passes through the volume of tissue including the bone gap, speeds regrowth, and encourages calcification.
  • the new Sheffield Ring Fixator from Orthofix includes collars made from such material, perforated with separate sets of holes oriented radially for the fixation pins and axially for the extendable connection means.
  • collars made from such material, perforated with separate sets of holes oriented radially for the fixation pins and axially for the extendable connection means.
  • Figure 19 illustrates another mode of use of the invention, in which electrodes 170a and 170b are placed on opposing inner surfaces of a tub or other container 172 holding water or other liquid 174 in which one or more conductive ionic salts, such as sodium chloride (table salt) or magnesium sulfate (Epsom salt), are dissolved.
  • Container 172 is itself preferably nonconductive, but if some parts of it, such as plumbing attachments, are conductive, it may be convenient to have them function as one or both of the electrodes, or as portions thereof.
  • the body part 176 to be treated is immersed in the conductive solution. Body part 176 will generally be that most affected by the condition to be treated.
  • a foot and lower leg might be treated as shown.
  • a suitable signal according to the principles of the invention is generated by a source 178 and passed through the solution and the immersed body part, from one electrode to the other, as described in the preceding sections and Figures.
  • the resistivity of liquid 174, including dissolved salts, preferably lies in the same range as that of living tissues, around 50 to 300 ohm-centimeters.
  • FIG. 20 illustrates yet another mode of use of the invention, for the purpose of healing chronic wounds such as diabetic or decubitus ulcers.
  • One electrode 180 is placed upon or within an electrically- conductive, sterile dressing 182, in direct contact with the wound surface 184. Electrode 180 is preferably placed directly over the wound surface as shown in the figure, but if for any reason this is impractical, one or more electrodes 180a, 180b and so forth may be placed adjacent to the wound instead.
  • Electrode 180 (or electrodes 180a, 180b and so forth) and dressing 182 are then preferably covered by an outer, nonconductive dressing 186.
  • the other electrode 190 is placed on healthy skin nearby, and preferably, if practical, on the opposite side of the limb or other body part 192 on which the wound is located, so that the distribution of treatment current 194 is substantially uniform across surface 184. Again, if the use of a single electrode is impractical or cannot give the desired current distribution, multiple electrodes 190a, 190b and so forth may be used instead.
  • Current 194 is supplied by a compact source 196, made according to the principles of the invention. Source 196 may optionally be attached to, or made a part of, outer dressing portion 186 as shown in the Figure.
  • the apparatus for generating the signal is another important feature of the present invention.
  • the invention makes it simple to generate any one or any combination of the signals just described using essentially the same, relatively simple circuit made up of inexpensive and widely-available, CMOS integrated circuit components.
  • CMOS integrated circuit components made up of inexpensive and widely-available, CMOS integrated circuit components.
  • a combination stimulator can easily be built combining interferential electrotherapy with powered muscle stimulation and perhaps also with other chosen waveforms, yet without the "overhead" of cost, bulk, power demand (with resulting short battery lifetimes) and high manufacturing setup charges which would likely be required for the same functions if implemented using microprocessor technology.
  • a waveform according to the present invention including any of those shown in Figure 4 or Figures 6 through 15, can be generated with an apparatus such as 200, shown in block diagram form in Figure 21.
  • Apparatus 200 includes the following functional blocks: a first frequency generator 202 and optional sequential switch (“sequencer”) 204 which provide the timing for primary intervals Tl, T2 and so forth; a second frequency generator 206 and optional sequencer 208 which provide the timing for secondary intervals tl, t2 and so forth; optionally, one or more electronically controlled switches, such as data multiplexers or solid-state analog switches, controlled by the outputs of sequencers 204 and 208 and generally indicated by 210; an array of passive components generally indicated by 212, from which specific combinations are selected by switches 210 if present; output means consisting either of one logic-level driver 214 or, preferably, of two such drivers 214a and 214b, each driving one of the output lines, as shown; output, filter 216 optionally including direct-current-blocking capacitors 218a and 218b, a transformer 220, a variable attenuator 222, high- frequency suppression means 224, or any combination of these, resulting in a modified output at terminals
  • the switches used in this invention are preferably CMOS analog switches: either the type used in a CD4016B or CD4066B integrated circuit (single-pole, single-throw) or in a CD4053B (single- pole, double-throw). Switches of these types may be used to carry either analog or digital signals, so long as they do not exceed the voltage range between the positive supply and ground. For simplicity in this and the following Figures, and to distinguish them from conventional, moving-contact switches or relays, these switches will be indicated by the following conventions. Single "bowtie” symbols, as in Figure 21, will indicate single-throw (CD4016B or CD4066B type) switches.
  • Doubled “bowties” (as, for example, switch 270 in Figure 23) will indicate double-throw (CD4053B type) switches. In each case, the lines entering the ends of the "bowtie” will be the switched lines while an arrow pointing in from the side represents the control input.
  • a CD4016B or CD4066B switch is turned on by a logic high ("1 ") input, and off by a logic low (“0") input.
  • small numerals "1" and "0" will be placed at the ends of the doubled bowtie symbol (again, as with switch 270 in Figure 23) to show which input state causes each connection to be made.
  • Frequency generators 202 and 206 are preferably astable oscillators, each formed by two inverting CMOS logic gates with resistive and capacitive feedback, so that each gate produces two complementary outputs switching alternatively between logic high and logic low voltages. Either one or both of these outputs may be used, depending upon the application. Specific examples of such oscillators will be shown in Figures 23 and those following it, and described in the accompanying text. Sequencer 204 is used if the primary cycle contains more than two primary intervals Tl and T2, or if one or more of these intervals is longer than the practical half-cycle time (time with output constantly either high or low) of frequency generator 202. Otherwise, generator 202 can produce the switching outputs directly as it passes through its inherent two-stage oscillation cycle.
  • sequential switch 208 is used if the secondary cycle contains more than two primary intervals tl and t2, or if one or more of these intervals is longer than the practical half-cycle time (time with output constantly either high or low) of frequency generator 206. Otherwise, generator 206 can produce the switching outputs directly as it passes through its inherent two-stage oscillation cycle.
  • Passive components 212 may consist of resistors, capacitors, diodes, or series or parallel combinations of such devices. Components 212 may affect the timing of frequency generators 202, 206, or both. Alternatively, some of switches 210 may control logic signals to select or de-select various circuit functions. In some cases it may be practical to combine frequency generators
  • Power may be supplied to the invention from the electrical mains (typically 120 or 240 volts A.C. at 50 or 60 Hz) using power-supply means well-known in the art. Since use of the mains poses some risk of electric shock, however, the invention is preferably powered instead by a battery 230, whose output is, for example, approximately between six and eighteen volts.
  • Battery 230 may be either a primary or a rechargeable type, but is more preferably a primary lithium battery because of this type's high power density and relatively flat discharge characteristics.
  • battery 230 is most preferably a stack of 3-volt lithium coin cells, such as CR2032's, enclosed and held together at their edges by a nonconductive sheath.
  • a power switch 232, a series diode 234, and/or a buffer capacitor 236 may be added to conserve battery life, eliminate any danger from improper battery installation, and minimize the effects of the battery's internal resistance.
  • CMOS microcontroller 250 for example, a Microchip PIC16F627), as shown in block form in Figure 22.
  • Frequency generators 202 and 206, and sequencers 204 and 208 are thus implemented with software modules in the microprocessor program, rather than with discrete, hard-wired components. No change in functionality occurs when this is done; the microprocessor merely takes over some or all of the timing and sequencing functions, so that the corresponding electronic switches 210 and passive components 212 connected to them (typically, any which help to generate the timing) can be eliminated. For some purposes, however, it may be advantageous to retain others of these switches and passive components, as shown, controlling them directly with the microprocessor outputs.
  • a first specific embodiment of the invention is shown in Figure 23.
  • this embodiment has been deliberately simplified so as to generate the three-stage prior art primary cycle, with one primary interval subdivided by a secondary cycle, which is shown in Figure 4 and described in U.S. Patent #6,535,767, or any of a family of alternative waveforms of the same general form but different primary cycle lengths.
  • the circuit shown is thus an alternative means of generating this waveform, illustrating the principles of the present invention by dynamically selecting components 212 which cause the lengths of the primary cycle intervals to differ.
  • a first frequency generator 260 consisting of two inverting CMOS logic gates 262a and 262b, a fixed resistor 264, a variable resistor 266, and two capacitors 268a and 268b which are alternately selected by switch means 270, runs freely at a frequency set chiefly by resistor 266 and the selected capacitor.
  • Logic gates 262a and 262b may be single gates in any type of CMOS integrated circuit able to operate at the battery supply voltage, but are preferably two of the gates in an integrated circuit of the CD4000B series, which provides buffered outputs.
  • Switch means 270 is preferably one section of a commonly- available CD4053B triple 2-channel, CMOS analog data multiplexer.
  • the small numerals "0" and “1 " at the ends of the symbol indicate the connections which it makes with the corresponding input signals.
  • a CMOS analog switch is placed between the output of the logic gate and any capacitor to which it is connected. Placing the switch on the opposite side of the capacitor could expose it to out-of-range voltages, with results difficult to predict.
  • the oscillator configuration shown is a common one, well-known in the art of circuit design. Assuming ideal component behavior, the cycle time, or time for one complete oscillation, is given by the equation
  • T CYC 2 R C ln(3) where R is the value of resistor 266, C is the value of the selected capacitor 268a or 268b, and ln(3) is approximately 1.0986.
  • the cycle time is thus proportional to both the value of the selected capacitor, and the value to which resistor 266 has been adjusted.
  • the output of generator 260 a square wave, drives a binary, decimal or other digital counter forming a ten-step sequencer 274.
  • this counter is a commonly-available CD4017B CMOS decade counter with decoded, "one-of-N" outputs where "N" is normally ten. For simplicity, it is shown on the schematic simply as a box with a clock input and ten numbered outputs.
  • steps 1 through 9 of sequencer 274 output 10 from the sequencer is at logic low ("0") and switch 270 selects capacitor 268a, while during step 10 the output is at logic high (“1") and the switch selects capacitor 268b instead.
  • the selected capacitor determines the length of the corresponding step.
  • steps 1 through 9 are equal in length (apart from startup transients) while step 10 has a different length.
  • capacitor 268a has a value between about 1.5 and about 2.7 times that of capacitor 268b, causing steps 1 through 9 to last longer than step 10 by the same ratio.
  • Resistor 266 may be either a simple potentiometer as shown, or a switch selecting any of a plurality of fixed resistors, singly or in combination.
  • resistor 266 has a range of possible values from about 15,000 ohms to about 1.5 million ohms, capacitor 268a has a value of 0.022 microfarad, and capacitor 268b has a value of 0.01 microfarad.
  • the value of resistor 264 is not critical, so long as it is at least twice the highest possible value of resistor 266. Given these preferred values, with resistor 266 set to a value of about 146,000 ohms, and assuming ideal behavior in all components, steps 1 through 9 of sequencer 274 take 7.05 milliseconds each, while step 10 takes 3.21 milliseconds. The resulting primary cycle of ten steps thus takes 66.7 milliseconds, for a primary frequency Fp of 15.0 Hz.
  • resistor 266 Other values of resistor 266 give different cycle lengths, but preserve the proportionality between the lengths of all steps. For the range from 15,000 ohms to 1.5 megohms, the corresponding primary frequencies (again assuming ideal response) range from 146 Hz down to 1.46 Hz.
  • sequencer 274 is in any of steps 1 through 8, both of output drivers 280a and 280b have their inputs pulled to logic "low" by resistors 282a and 282b respectively, so that their differential output voltage is zero. Steps 1 through 8 therefore appear as a single, continuous interval Tl, during which the output maintains a constant output state of zero current or voltage.
  • sequencer 274 When sequencer 274 is in step 9, it turns on a second frequency generator 290, consisting of a two-input CMOS NAND gate 292, an inverting CMOS logic gate 294, three fixed resistors 296, 298 and 300, a diode 302, and a capacitor 304. Again, apart this time from the presence of resistor 300 and diode 302, which permit the generation of an asymmetric output waveform, this is a common oscillator configuration well-known in the art of circuit design. The functioning of the oscillator, when modified by adding the extra resistor and diode, was explained in detail in U.S. Patent #6,011,994, here incorporated by reference.
  • the second NAND gate input when held at logic high while the sequencer is in step 9, acts as an enabling input which turns on generator 290 only during this interval.
  • Rs is the value of resistor 298 alone
  • Rp is the value of the parallel combination of resistors 298 and 300 plus a small term contributed by diode 302
  • C is the value of capacitor 304
  • ln(3) is approximately 1.0986.
  • the duty cycle here represents the proportion of time spent in the more positive polarity as represented in figure 23, rather than in the more negative polarity.
  • Rs, Rp and C are chosen to place FOSC in the range between 1000 and 2000 KHz, and DC in the range between 67% and 95%, satisfying condition (g) in the previous section. More preferably, FOSC lies in the range between 4000 and 4500 Hz and DC is about 88%.
  • resistors 298 and 300 and capacitor 304 stock component values of 180,000 ohms, 33,000 ohms, and .001 microfarad respectively.
  • the signals on lines 306a and 306b are sent respectively to drivers 280a and 280b through switches 310a and 310b, here formed by the two remaining sections of the same CD4053 chip whose first section forms switch 270, but controlled by output 9 from the sequencer.
  • switches 310a and 310b here formed by the two remaining sections of the same CD4053 chip whose first section forms switch 270, but controlled by output 9 from the sequencer.
  • the switches are both shown as if single-pole, with a small numeral " 1 " beside each to show that this is the logical control level which turns it on.
  • switches 310a and 310b receive a logic low control input, and thus make no connection. During step 9, however, they receive a logic high input, turn on, and pass the complementary output signals through to the drivers. This creates a secondary-cycle output signal having the previously- described characteristics during step 9, which thus represents T2 in the primary cycle.
  • generator 260 is once again turned off, and its outputs are disconnected from the output drivers. Diode 312, however, now feeds the positive logic signal from output 10 of the sequencer to the input of driver 208a, overwhelming the effect of resistor 282a, while the input of driver 280b remains held at logic low by resistor 282b.
  • capacitors 314a and 314b form an output filter blocking any remaining net direct current from appearing at outputs 316.
  • the circuit of figure 23 is significantly more complex than those described in U.S. Patents #6,011,994 and #6,535,767, it has the advantage of permitting all primary timing intervals to be set by the single variable resistor 266 so that, by changing the value of this resistor, a user can change the pulse-train repetition frequency Fp without affecting the charge balance of the resulting output and without any effect upon the secondary cycle, which maintains a constant frequency F (equal to FOSC above) and duty cycle DCs.
  • a second specific embodiment of the invention is shown in Figure 24.
  • This implementation can produce either the output waveform of Figure 7 or that of Figure 16, or any one of a family of alternative waveforms having the same general form but different primary cycle lengths, secondary cycle lengths, frequency characteristics, or any combination of these.
  • a first frequency generator 330 and sequencer 332 produce a primary cycle.
  • Frequency generator 330 and sequencer 332 are much the same as in the previous embodiment, except that in the CD4017B chip forming the sequencer, output 5 is connected to the reset input so that, on reaching this state, the sequencer immediately (typically within 200 nanoseconds) returns to step 1.
  • the primary cycle thus consists of only four steps Tl, T2, T3 and T4 each corresponding to just one step of the sequencer.
  • the lengths of the primary intervals are determined in part by switched capacitance in frequency generator 330.
  • capacitors 334a, 334b and 334c all of which are equal in value.
  • capacitor 334a is connected at all times while the others are connected or disconnected through switches 336a and 336b, respectively, depending upon the sequencer output.
  • a fixed resistor 338 and variable resistor 340 here function in the same way as resistors 264 and 266, respectively, in the previous implementation.
  • R is the value of variable resistor 340 and C is that of capacitor 334a.
  • the value of fixed resistor 338 is not critical so long as it is at least twice the maximum value of resistor 340.
  • a second frequency generator 344 runs at all times except when switched off by inverter 342 during Tl .
  • Generator 344 is exactly like generator 290 in Figure 23, except that the extra diode and resistor there, used to produce asymmetric oscillation, are not present here.
  • generator 344 produces complementary square-wave outputs on lines 346a and 346b. Also connected to the outputs of sequencer 332 are NOR gates
  • Gate 348 is connected to outputs 2 and 3, producing a logic low output during intervals T2 and T3 and a logic high output during intervals Tl and T4.
  • gate 350 is connected to outputs 3 and 4, producing a logic low output during T3 and T4 and a logic high during Tl and T2-
  • the output of gate 348 is fed to one input of a third NOR gate 352, whose other input is the square-wave signal on line 346b.
  • gate 352's output is at constant logic low throughout Tl and T4 , while during T2 and T3 it is the signal on line 346b, inverted.
  • gate 350 is fed to one input of a fourth NOR gate 354, whose other input is the square-wave signal on line 346a.
  • gate 354's output is at constant logic low throughout Tl and T2, while during T3 and T4 it is the signal on line
  • 360b, 360c and 360d are Tl, T2, T3 and T4 respectively; traces 346a and 346b represent the voltages on the like-numbered signal lines; and traces 348, 350, 352 and 354 represent the outputs of the like-numbered gates.
  • Trace 360 is simply the difference between traces 352 and 354. Note that trace 360 is identical with that in Figure 7.
  • the signal represented by trace 360 has some of the characteristics of the sinusoidally-modulated signal which results from the interference of two sine waves at slightly different frequencies. This is the classic signal used in interferential electrotherapy, in which it is created by applying sine-wave signals at two slightly different frequencies to the body through separate electrode pairs. Such a signal is represented by trace 362.
  • the signals of traces 360 and 362 are alike in that both have alternating periods of maximum and minimum intensity, with the minimum lasting only a short time while the maximum is relatively long. They differ primarily in harmonic content: since the signal of trace 360 has sharp corners, it contains large amounts of higher frequencies, while the signal of trace 362 does not since the waves are approximately sinusoidal.
  • the signal of trace 360 may be used for electrotherapy just as it is. Some charge imbalance is present during T2 and T4, but since the waveforms during these intervals are nominally equal and of opposing polarities, it will largely be cancelled out. Any residual imbalance may be canceled, if necessary, by direct-current-blocking capacitors. In some cases, however, a more nearly "classical" interferential waveform may be desirable.
  • the higher-frequency components may be removed by bandpass or low-pass filtering, preferably using active operational-amplifier circuits.
  • Direct-current output components may simultaneously be blocked.
  • the single-operational-amplifier, resonant bandpass filter shown schematically in circuit block 356a will perform both of these functions for the output signal of gate 352, by blocking all frequencies outside a chosen, relatively narrow band. Since this circuit is of a type well-known in the art of active filter design, its functioning will not be discussed further here.
  • a second, identical filter 356b for conciseness shown here only as a blank box, performs the same functions for the output of gate 354.
  • both filters may be made using a low-power, dual operational amplifier integrated circuit such as an LF353N or TL082.
  • Trace 364 represents the result of such filtering. As is readily apparent, the signal has the same overall characteristics as before but the high-frequency cycles are now considerably more rounded, showing that most harmonics have been eliminated. Note that trace 364 is identical with that in Figure 16.
  • a third specific embodiment of the invention, shown in Figure 26, is designed to produce from the same compact device, and at the user's choice, either an asymmetrically-modulated pulse-train signal similar to that of Figure 4, suitable for tissue healing stimulation and pain relief; a square-wave-modulated signal of similar form, suitable for muscle stimulation; or a quasi-sinusoidal signal like that of the previous embodiment, suitable for interferential stimulation.
  • a single frequency generator 400 of conventional form, both directly generates the secondary cycle and drives a binary counter 402, such as a CD4040B integrated circuit, which together with a frequency-selecting switch 404 and sequencer 406, generates the primary cycle.
  • Counter 402 thus functions as secondary frequency generator 206 as shown in Figure 21.
  • Generator 400 preferably runs at a frequency in the range between 1000 and 200 KHz, and more preferably in the range between 4000 and 4500 Hz.
  • the operating frequency will be assumed to be 4096 Hz (2 Hz) in the explanation which follows.
  • the basic principles, however, are independent of the actual frequency.
  • Generator 400 is followed by a pulse-shaping network made up of capacitor 410 and resistor 412, such that, after squaring of the pulses by a following CMOS gate,
  • K is a numerical constant determining the duty cycle of the resulting pulse-train waveform.
  • K lies in the range from two to fourteen, yielding duty cycles in the range from 67% to 95%, thus satisfying condition (g) in the previous section. More preferably, K is about 5.75, yielding a duty cycle close to 88%.
  • Switch 414 then permits either the symmetric or the asymmetric version of the output waveform to be chosen.
  • the signal is then buffered by a gate 416, which may be inverting, as shown.
  • Binary counter 402 has a plurality of taps representing different binary divisors.
  • any one of these taps, or preferably any one of a chosen subset of them, may be selected using switch 404.
  • the signal at the selected tap then forms the clock input to sequencer 406, which is configured for eight steps by connecting together the step 9 output and reset input.
  • the primary cycle frequency represents a further division of the clock frequency by eight. For example, with the subset of selectable taps shown in the Figure, and with an oscillator frequency of 4096 Hz:
  • OR gate 424 combines the step 1, 2, 3 and 4 output signals from sequencer 406.
  • OR gate 426 combines the step 4, 5 and 6 signals.
  • Two-pole, three-position switch 440 then selects some combination of signals 420, 422, 424 and 426 so that the signals selected by the two poles appear on lines 442a and 442b respectively.
  • position "A” both poles select signal 424.
  • position "B” both poles select signal 420.
  • position "C” one pole selects signal 422 while the other selects signal 426, so that these signals appear on lines 442a and 442b respectively.
  • AND gate 444 then combines the signals from gate 416 and on line 442a, so that the carrier signal is passed through whenever line 442a is high.
  • NAND gate 446 does the same for the signals from gate 416 and on line 442a, except that the carrier, when passed through, is also inverted so that the carrier signals from gates 444 and 446 are complementary.
  • gates 444 and 446 may either be high-current-output types, or be followed by buffer amplifiers as was shown in Figure 21.
  • Filter 448 then preferably blocks DC and frequency components above about 40 KHz (10 Fs) and steps up the output voltage if necessary, yielding a differential output at terminals 450.
  • Filter 448 may optionally be given a plurality of different filtering and/or voltage step- up characteristics, also switch-selected, to suit the different waveforms and their intended applications.
  • Trace 404 represents the clock input to sequencer 406.
  • Trace 416 represents the selected carrier waveform, here shown as asymmetric; the cycle length is exaggerated for clarity.
  • Trace 420 represents the Step 1 output, and traces 424, 426, and 432 the signals on the corresponding lines in Figure 26.
  • Traces 450a, 450b and 450c represent the resulting differential output signals 450 for positions "A,” “B” and “C” of switch 440, respectively, neglecting any effects of filter 448.
  • Switches 404, 414 and 440 may be either electronic switches, such as those in a CD4016B, CD4051B, CD4052B or CD4053B integrated circuit, or conventional mechanical switches. In either case, it may be desirable to limit the possible combinations of settings to some conveniently small number representing the output waveforms which are the most generally useful. For example, all choices could be combined in a custom, multipole rotary switch, similar to those used in digital multimeters, with one position yielding each chosen combination and one more position turning the stimulator off.
  • the muscle-stimulating waveform consists of two-second pulse bursts causing muscle fibers to contract, alternating with two-second periods of no signal, permitting them to relax.
  • the tissue-stimulating waveform is similar to that generated by the first embodiment of the invention, while the interferential waveform is similar to that generated by the second embodiment.
  • a fourth specific embodiment of the invention is designed to produce a nonsinusoidal, asymmetric but charge-balanced output similar to that which was shown in Figure 15, but also containing the secondary- cycle frequency shift which was shown in Figure 12. This embodiment is shown in Figure 28.
  • a frequency generator 500 similar to that in the previous embodiment, drives a sequencer 502 having ten steps just as in the first embodiment described.
  • generator 500 Since generator 500 has no time-varying components, it runs at a constant rate, which is preferably about one step per second. The full cycle of sequencer 502 is thus completed in about ten seconds.
  • a NOR gate 510 combines sequencer outputs 2, 3, and 4, producing a logic low output during these steps and logic high otherwise.
  • a second NOR gate 512 does the same with outputs 1 and 5, producing a logic low during these steps and logic high otherwise.
  • These outputs define Tl through T4 so that Tl equals step 1, with the output of gate 510 high but that of 512 low; T2 equals steps 2, 3, and 4 combined, with the output of gate 510 low but that of 512 high; T3 equals step 6, with the outputs again as in Tl; and T4 equals the sum of steps 6 through 10.
  • a NAND gate 514 then combines the outputs of gates 510 and 512, so that its output is at logic low during T4 but logic high at all other times. (An identical output could be obtained from a NOR gate fed by sequencer outputs 6 through 10 or, in a CD4017B or equivalent integrated circuit, directly from the C out ("Carry Out") pin.
  • a second frequency generator 520 is made up of a NAND gate 522, an inverter 524, three resistors 526, 528 and 530, a diode 532, a capacitor 534a which is permanently connected, and a second capacitor 534b which can be placed temporarily in parallel with it through switch 536, controlled by gate 510 so that it is disconnected during T2-
  • Generator 520 produces a single output on line 538.
  • Gate 522 is controlled by the output of gate 512, so that generator 520 runs only during T2 and T4, while signal 512 is high, producing an oscillating output on line 538, while during Tl and T3 signal 512 is low and oscillator 520's output is also held constantly low.
  • Resistors 526, 528 and 530 preferably have values of about 2.2 megohms, 270,000 ohms, and 27,000 ohms, respectively, and capacitors 434a and 434b, about 0.01 microfarad and one microfarad respectively.
  • capacitors 434a and 434b With this circuit configuration and with these values, during T2 only capacitor 534a is in the circuit and the output of generator 520 spends alternate periods of about three milliseconds at logic high and 0.3 millisecond at logic low, for a secondary frequency Fs of about 300 Hz.
  • the value of capacitor 534b is added to that of capacitor 534a, and the generator output spends about 300 milliseconds high and 30 milliseconds low, for a secondary frequency of about 3 Hz.
  • An XOR (exclusive OR) gate 540 receives as inputs the signal on line 538 and that from gate 510, which as stated above is at logic high during Tl, T3 and T4 but at logic low during T2- As a result, gate 540 passes the signal from line 538 unchanged during T2 but inverts it at all other times.
  • a second XOR gate 542 receives as inputs the signal on line 538 and that from gate 514, which is at logic high during Tl, T2 and T3 but at logic low during T4. As a result, gate 540 passes the signal from line 538 unchanged during T4 but inverts it at all other times.
  • the outputs of gates 540 and 542 respectively feed buffer amplifiers 544a and 544b. The output from this embodiment of the invention consists of the differential signal between these two buffer outputs. The resulting signals are illustrated in Figure 29, in which trace
  • trace 538 is the output of generator 520 on line 538; traces 510, 512, 514, 540 and 542 are the outputs of the like-numbered gates; and trace 546 is the differential output signal from buffers 544a and 544b.
  • the secondary cycle lengths during T2 are shown, and the number of cycles correspondingly reduced, so that the change in polarity between T2 and T4 5 corresponding to that which was shown in Figure 5, is evident. Note that apart from this reversal, trace 544 is substantially identical with the trace in Figure 12. In some cases, intermittent rather than continuous treatment may be desirable.
  • the patient may be best to allow the patient to control the dosage: starting the treatment upon the press of a button, allowing the signal to be generated for a preset period such as 30 or 60 minutes, then turning it off until the patient presses the button again, and so forth.
  • the "off" period could also be preset so that the device would cycle continuously between “on” and “off periods of a half-hour to several hours each, or require a preset minimum "off interval before accepting another button press.
  • the output of frequency generator 500 may conveniently be applied to a binary or other counter chain 550, much as in the previous embodiment, whose output 552 drives an additional input of gate 512.
  • Signal 552 may either be taken from a single output as shown, or be derived from several such outputs: for example, by using a NOR gate in an arrangement similar to that of gate 510, followed by an inverter. Signal 552 is initially at logic low, enabling gate 512 and frequency generator 520 to operate as previously described. Upon the attainment of a specific count in counter 550, however, signal 552 changes to logic high, forces gate 512's output to logic low, and thus disables generator 520 and forces the differential output signal from buffers 544a and 544b to zero. Depending upon the arrangement of counter 550, further counting may then be disabled so that there will be no further output from the buffers until the counter is reset to zero, for example by the press of a button as previously described.
  • a fifth specific embodiment of the invention is designed to produce a nonsinusoidal, approximately exponentially-decaying signal whenever it is triggered by an external source.
  • An idealized curve of symmetrical exponential decay is shown in Figure 30 by trace 600; note that this reproduces trace 110 in Figure 5, except that it is shown on a larger scale.
  • Trace 602 shows an approximation made up of five intervals 604a, 604b, 604c, 604d and 604e, each containing a carrier signal with steady amplitude which steps downward from each interval to the next, plus an interval 604f of zero amplitude.
  • interval 604f represents primary interval Tl
  • intervals 604a, 604b, 604c, 604d and 604e represent T2, T3, T4, T5 and T6 in turn.
  • the Figure shows a representative portion 604f of Tl at the start, followed by the other five primary intervals in turn, and finally a representative portion 604f ' of Tl from the next primary cycle. So that the steps in trace 602 may be more clearly seen, the vertical hatching which was used in Figure 5 to indicate the presence of a secondary cycle is here omitted. Intervals in the primary cycle, beginning with T2 and ending with
  • T6 may be either equal or successively longer.
  • intervals T2, T3 and T4 all have the same length
  • interval T5 has twice this length
  • interval T6 has four times this length.
  • the relative amplitudes of the signal during T2, T3, T4, T5 and T6 are close to 100%, 80%, 60%, 40% and 20%, respectively.
  • the amplitude during Tl is zero.
  • Tl may be either fixed in length, yielding a periodic signal, or arbitrarily long, yielding a signal which is aperiodic.
  • Trace 606 shows an oscillating signal which decays exponentially with an amplitude following the curve of trace 600.
  • Trace 608 shows a signal according to the principles of the invention which follows approximately the same decay curve, using multiple levels of voltage or current as indicated by trace 602.
  • Trace 610 shows a more practical signal according to the principles of the invention, in which only three voltage or current levels are used but the effective amplitude is decreased by changing the time relationships of these levels within the secondary cycle, again as indicated by trace 602. Note that trace 610 is identical with the trace which was previously shown in Figure 11.
  • Figure 31 shows an example of a circuit able to generate the waveform of trace 610, or any of a large family of similar ones.
  • signals of this general form when applied at relatively high intensities, have been shown to devitalize some microorganisms in vitro and might thus be useful in the preservation of foodstuffs or beverages, or in the sterilization of pharmaceutical materials or drinking water. Since it is not intended for direct connection to a human or animal body, the circuit shown in Figure 31 might be powered either by batteries like the preceding embodiments, or by the electric mains.
  • a first frequency generator 620 and sequencer 622 generate ten timing steps. Sequencer 622's "reset" input is connected to an external input line 624 which is normally held at logic low, for example by a resistor 626.
  • Generator 620 is of the general form previously described, consisting of inverting gates 630 and 632, resistors 634 and 636, and capacitor 638, but differs in that a switch 640, when turned on, connects the junction of resistors 634 and 636 and capacitor 638 to the positive supply. This halts the generator with the output of gate 632 also high, so that capacitor 638 is essentially discharged with both terminals at logic high.
  • switch 640 re-opens, generator 620 then re-starts from a known state and thus with known and reproducible initial timing intervals before its next transitions. Assuming ideal component characteristics,, the interval between the switch's opening and the output's next transition to logic high, advancing sequencer 622, will be
  • sequencer 622 Upon sequencer 622's reaching step 10, this output raises one input of OR gate 642 high, forcing its output also high. This closes switch 640, stopping generator 620 as already described. Since the sequencer can then receive no more clock pulses, it remains in this state until it is reset to step 1 by a logic high at input 624. Input 624 also feeds gate 642, so that generator 620 remains disabled as long as the input remains at logic high. Only when input 624 returns to logic low will generator 620 begin again to oscillate: advancing sequencer 622 to step 2 after about 1.792 R C, then to each of the following steps at intervals of about 2.197 R C, until it again reaches step 10 and halts awaiting another reset input.
  • a second frequency generator 650 is identical with generator 620, save that it operates at a sufficiently higher frequency that at least two, and typically several hundred, secondary cycles occur during each step of sequencer 622, and that complementary outputs are taken from inverting gates 652 and 654.
  • the operating frequency of generator 650 is the carrier frequency.
  • generator 650 contains a switch 656 which, when turned on, halts it in a reproducible state. Switch 656 is driven directly by output 10 of sequencer 622, so that it is halted during step 10 but runs at all other times, including Tl .
  • Outputs 4 and 5 of sequencer 622 are combined by OR gate 660, producing a single output which is at logic high throughout steps 4 and 5.
  • outputs 6, 7, 8, 9 and 10 are combined by OR gate 662, producing a single output which is at logic high throughout steps 6 through 10.
  • Resistors 666a, 666b, 666c and 666d are successively smaller in value, and are connected to a common line 668, to which the output of gate 654 (complementary to that of gate 652) is also connected through a capacitor 670.
  • traces 652 and 654 represent the outputs of the like-numbered gates
  • traces 668a, 668b and 668c represent the voltage on line 668 under three different operating conditions and over a few cycles of the carrier frequency: trace 668a with none of resistors 656a through 656d selected, trace 668b with a relatively large-valued resistor selected, and trace 668c with a relatively smaller- valued resistor selected.
  • Each of voltages 668a, 668b and 668c rises or falls abruptly with each upward or downward transition of gate 654.
  • Diodes 674a and 674b prevent this voltage from significantly exceeding the supply voltage range.
  • voltage 668 decays toward voltage 652 with a time constant determined by the values of capacitor 670 and the selected resistor.
  • XOR gate 680 compares voltages 654 and 668. Since a 4000B-series CMOS gate undergoes output transition at an input voltage about halfway between the supply voltages (indicated by horizontal, hatched line 672 in Figure 32), gate 680 generates a logic low output during each half-cycle of generator 650 for so long as the difference between voltages 654 and 668 remains less than one-half the supply voltage, and a logic high output thereafter, as indicated by traces 680a, 680b and 680c respectively for the conditions of no resistor, high-valued resistor and low-valued resistor selected.
  • OR gates 682a and 682b then compare voltage 680 with voltages 652 and 654 respectively, each generating a logic low pulse corresponding to that from gate 680 during the corresponding logic-low half cycle of voltage 652 or 654, respectively. Buffered (and preferably voltage-amplified) by output buffers 684a and 684b, these create a differential output 686 as indicated by traces 686a, 686b and 686c for the respective resistor selections.
  • Step 10 when generator 650 is disabled, resistor 666d remains selected, the inputs of gate 680 are thus pulled quickly to and remain at opposite logic levels, and its output generates a constant logic high which is passed through to both outputs so that the differential voltage between them is zero.
  • Step 10 of sequencer 622 represents interval Tl of the primary cycle, when the sequencer is halted with generator 650 also turned off and with zero differential output. In step 1, either with line 624 high or until the first transition of gate 632's output after line 624 goes low again, generator 650 runs but no resistor is selected.
  • the voltage on line 668 (trace 668a) is essentially the same as that coming from the output of gate 654 and the differential output is at maximum duty cycle: a square wave at the carrier frequency, running from full positive to full negative output voltage or current. This represents interval T2 of the primary cycle.
  • step 2 step 3, steps 4 and 5 together, and steps 6, 7, 8 and 9 together, successively lower resistor values are selected, causing the output to take the form of successively narrower pulses, alternately of full positive and full negative output voltage or current, separated by successively longer periods of zero output, thereby approximating exponential decay through progressive changes in duty cycle.
  • the signal (considered as pairs of one positive and one negative pulse each) repeats at the carrier frequency but with successively greater portions of time spent at zero voltage or current.
  • These sequencer steps or step combinations thus represent T3, T4, T5 and T ⁇ of the primary cycle.
  • the sequencer returns to step 10 (Tl) and the cycle will then repeat itself upon receipt of another positive pulse at input 624.
  • the resulting cycle may be rendered periodic, if desired, simply by applying periodically-spaced pulses to the input, separated by intervals longer than nine cycles of generator 620.
  • the cycle may be started aperiodically each time a specified set of process conditions, such as the correct placement of a vessel or volume of material to be treated between the output electrodes, is attained.
  • a sixth specific embodiment of the invention illustrated in Figure 33, illustrates the use of a multistep secondary cycle and sequencer in generating outputs like those of the preceding embodiment, but with greater consistency and precision.
  • a primary frequency generator 620 and secondary frequency generator 650 are identical with like-numbered components in the previous embodiment and function in the same way, save that here generator 650 operates at ten times the desired carrier frequency. For simplicity, these generators are shown in Figure 33 only in outline.
  • a primary sequencer 622 and OR gates 642, 660 and 662 are also identical with like-numbered components in the previous embodiment, except that here gate 662 combines the signals only from steps 6 through 9. Apart from its lack of a connection to gate 662, the output from step 10 of the sequencer operates exactly as in the preceding embodiment.
  • the output of generator 650 now provides a clock input to sequencer 700, which like sequencer 622 is configured for a cycle of ten equal steps. Sequencer 700's "reset" input is grounded, and not shown in the Figure. Like those of sequencer 662, also, the outputs of sequencer 700 are combined by OR gates to yield more complex outputs.
  • Gate 702 combines outputs 1 and 6 yielding a signal with a 20% duty cycle, while gate 704 combines outputs 4, 5, 9 and 10 yielding a signal with a 40% duty cycle, both at twice the carrier frequency (one-fifth the frequency of generator 650).
  • Signal 704 is inverted by gate 706a, and signal 702 by gate 706b, yielding signals of like frequency but at 60% and 80% duty cycle, respectively.
  • a third OR gate 708 combines outputs 1, 2, 3, 4 and 5 of sequencer 700, yielding a signal at 50% duty cycle at the carrier frequency.
  • a CD4017B package already includes such a gate, producing an output "Cout" ("carry out") which is normally used in combining a plurality of such chips to form a multi-stage counter; hence, gate 708 is not shown in the Figure and only its output line is labeled. If a different type of integrated circuit is used to form sequencer 700, gate 708 may need to be added externally. Signals 702, 704, 706a, 706b and 708, representing the outputs of the like-numbered gates, are shown in a row across the top of Figure 34. AND gate 710 combines the signal from gate 662, representing steps 6 through 9 of sequencer 622, with the signal from gate 702, representing a 20% duty cycle.
  • AND gate 712 combines the signal from gate 660, representing steps 4 and 5, with that from gate 704, representing a 40% duty cycle; AND gate 714 combines the signal directly from step 3 with that from gate 706b, representing a 60% duty cycle; and AND gate 716 combines the signal directly from step 2 with that from gate 706a, representing an 80% duty cycle. Note that the signal from step 1 of sequencer 622, carried on line
  • OR gate 720 then combines the signal on line 718 with those from
  • the resulting signal is a rectangular pulse at twice the carrier frequency, whose duty cycle varies with the step of sequencer 622: 100% (always high) in step 1 (T2), 80% in step 2 (T3), 60% in step 3 (T4), 40% in steps 4 and 5 (T5), and 20% in steps 6 through 9 (T6). Since sequencer 622's step 10 output is not connected to gate 662, the gate's output signal is continuously low during this step (Tl), representing a duty cycle of zero.
  • Sequencer 700's "Cout" signal 708, as stated above, is a square wave at the carrier frequency, while signal 720 runs at twice this speed.
  • one pulse of signal 720 falls within each half-cycle of signal 708: one while it is high, the other while it is low.
  • Inverter 724 taking signal 708 as its input, creates a second, complementary square wave: high when signal 708 is low, and low when it is high.
  • AND gate 730 then combines signals 708 and 720, so that its output consists of pulses of the same lengths as in signal 720, but only during the positive half-cycle of signal 708.
  • AND gate 732 combines signals 720 and 724, so that its output consists of pulses of the same lengths as in signal 720, but only during the negative half-cycle of signal 708.
  • the pulses from gates 730 and 732 thus alternate: one from gate 730, one from gate 732, another from gate 730, and so forth.
  • these signals create a differential output 686 which is closely similar to that of the preceding embodiment, approximating an exponentially-decaying sine-wave signal through a plurality of time periods containing rectangular waves having successively decreasing duty cycles.
  • the timing is all-digital, it is more accurate and reproducible. All of the above relationships may be expressed more concisely by writing Boolean expressions for the various signals:
  • a compact, double- sided printed circuit board and a small, lightweight housing to contain this board and the battery.
  • a housing is preferably made from molded plastic or a similar material, preferably with a pocket clip or other means for convenient mounting to a bandage, cast, wrist or other band, article of clothing, container of conductive liquid, or the like. More preferably, the housing is no larger than necessary to hold the described devices and the circuit board or boards which bear them.
  • suitable housings need be no larger than approximately 5 cm x 6 cm x 2 cm (about 2.0" x 2.5" x 0.75") or thereabouts, and in some cases may be significantly smaller.
  • housings may need to be somewhat larger. Since in a typical implementation the circuit board and housing are small, and since only widely-available, off-the-shelf electronic components are used, manufacturing costs will also typically be quite low. For applications wherein the treatment is slightly more complicated, where for example, more precise delivery of stimulation is required and/or where more delicate adjustment of signals is necessary, a technician or physician may employ an in-house industrial version of this invention for use on patients.
  • An apparatus according to the invention is therefore lightweight, compact, self-contained, cost-effective to manufacture and maintain, convenient to carry or wear for extended periods, and able to generate the signals just described and deliver them efficiently through conductive means as previously defined and as illustrated, for example, in Figures 17 through 20.
  • Power is furnished by compact and inexpensive batteries, typically needing replacement only once in several weeks of use. Since only low voltages and currents are used and there is no connection to the electric mains, the apparatus does not pose a shock hazard even in case of malfunction, and thus is safe for unsupervised home use without any need for special training.
  • the present invention comprises an apparatus for generating an electrical signal for use in biomedical applications, said electrical signal comprising: (a) at least four relatively longer primary timing intervals Tl, T2, T3, T4 and others if present, forming in succession a repeating primary cycle, said primary cycle having a frequency; (b) at least two relatively shorter secondary timing intervals tl, t2 and so forth, into which at least one of said primary timing intervals is divided and which form in succession a repeating secondary cycle throughout its length, said secondary cycle having a frequency, said frequency lying below 200 kHz; while at least one other of said primary timing intervals is not so divided; (c) a plurality of substantially constant voltage or current levels Ll, L2 and so forth; (d) selection of one of said voltage or current levels during each of said secondary intervals within a said primary interval which is so divided, or during the whole of said primary interval if it is not so divided: said levels, selected in succession throughout the course of said primary cycle, thereby forming
  • the present invention comprises a method for generating an electrical signal for use in biomedical applications, said method comprising: (a) generating at least four relatively longer primary timing intervals Tl, T2, T3, T4 and others if present, forming in succession a repeating primary cycle, said primary cycle having a frequency; (b) generating at least two relatively shorter secondary timing intervals tl, t2 and so forth, into which at least one of said primary timing intervals is divided and which form in succession a repeating secondary cycle throughout its length, said secondary cycle having a frequency, said frequency lying below 200 kHz; while at least one other of said primary timing intervals is not so divided; (c) generating a plurality of substantially constant voltage or current levels Ll, L2 and so forth; (d) selecting one of said voltage or current levels during each of said secondary intervals within a said primary interval which is so divided, or during the whole of said primary interval if it is not so divided: said levels, selected in succession throughout the course of said primary cycle, thereby forming
  • the present invention comprises an apparatus for generating an electrical signal comprising: means for generating primary timing intervals and secondary timing intervals into which at least one primary timing interval is divided, said primary timing intervals forming a charge balanced primary cycle.
  • the apparatus is effective in relieving chronic, intractable pain, acute post-traumatic pain, pain resulting from nerve irritation, pain resulting from diabetic neuropathy, pain resulting from muscle spasms, and pain resulting from compressed nerves.
  • a benefit of the present invention is the reduced requirement for pain relief drugs.
  • the apparatus and methods of the present invention can reduce general swelling, accelerate the resolution of unwanted inflammation, accelerate the healing of spinal disk injuries, relax muscle spasms, maintain or increase the range of motion of arms and/or legs, and be used as an immediate post-surgical stimulation of muscles to prevent venous thrombosis.
  • the present invention is also effective in treating and accelerating the healing of wounds, including, but not limited to, traumatic wounds, surgical incisions, burns, chronic wounds, including, but not limited to, diabetic ulcers, venous ulcers, arterial ulcers, decubitus ulcers.
  • the present invention is effective in accelerating the healing of strained or torn ligaments or tendons, accelerating the healing of torn muscle tissue.
  • the present invention is also effective in preventing or retarding muscle atrophy due to disuse or prolonged bed rest.
  • the present invention is also useful in regenerating damaged nerves.
  • the present invention is especially useful in increasing the survival of skin grafts and hair plugs.
  • the present invention is effective in improving the incorporation of synthetic implants such as bone powder and prostheses such as artificial joints (e.g., knees and hips).
  • the present invention is useful in treating sprained ankles, torn knee ligaments, sciatica, back muscle spasm, torn rotator cuff, tennis elbow, carpal tunnel syndrome, ulnar nerve syndrome, temporomandibular joint syndrome and pain from abscessed teeth.
  • the present invention can be used transcranially to relieve insomnia, depression, anxiety and to promote relaxation and mental alertness.
  • the present invention is useful in promoting angiogenesis including, but not limited to, increasing local blood circulation, increasing blood flow to areas of traumatic injury, increasing blood flow to areas of chronic skin ulcers.
  • the present invention is also useful in modulating blood coagulation. While not wanting to be bound by the following hypothesis, the apparatus is believed to operate directly at the treatment site by enhancing the release of chemical factors such as cytokines which are involved in cellular responses to various physiological conditions. This results in increased blood flow and inhibits further inflammation at the treatment site, thereby enhancing the body's inherent healing processes.
  • the present invention is especially used in accelerating healing of simple or complex bone fractures including, but not limited to, bones sawed or broken during surgery.
  • the present invention can be used to promote fusion of vertebrae after spinal fusion surgery.
  • One of the areas where the present invention can also be used is to accelerate the healing of damaged or torn cartilage.
  • the present invention can be used to accelerate the healing (epithelialization) of skin wounds or ulcers.
  • the following conditions provide a representative listing of conditions and ailments for which the present invention may be useful: relief of chronic intractable pain, relief of acute posttraumatic or postsurgical pain, reduction of pain resulting from nerve irritation (hyperalgesia), reduction of pain resulting from diabetic neuropathy, reduction of pain resulting from muscle spasm, reduction of pain resulting from trapped or compressed nerves, reduction of requirement for pain relief drugs, reduction of swelling, acceleration of resolution of inflammation, acceleration of healing of spinal disk injuries relaxation of muscle spasms, muscle re-education, maintain or increase range of motion, immediate post-surgical stimulation of calf muscles to prevent venous thrombosis, acceleration of healing of traumatic wounds, acceleration of healing of surgical incisions, acceleration of healing of burns acceleration of healing of chronic wounds (diabetic, venous, arterial and decubitus ulcers), acceleration of healing of strained or torn ligaments, acceleration of healing of strained or torn tendons, acceleration of healing of torn muscle tissue, prevention or retardation of disuse atrophy, retard
  • Additional applications of the present invention result in the acceleration of healing of fresh, simple bone fractures, of complex (multiple or comminuted) bone fractures, of bones sawn or broken during surgery and fusion of vertebrae after spinal fusion surgery.
  • the present invention may be used to treat nonunion fractures; treat, prevent or reverse osteoporosis; treat, prevent or reverse osteopenia; treat, prevent or reverse osteonecrosis; retard or reverse formation of woven bone (callus, bone spurs), retard or reverse bone calcium loss in prolonged bed rest, retard or reverse bone calcium loss in microgravity.
  • the present invention may be used to increase local blood circulation, increase blood flow to areas of traumatic injury, increase blood flow to areas of chronic skin ulcers and to modulate blood clotting.
  • the present invention may also be used for the adjunctive treatment of tendonitis, modulate local immune system response, modulate systemic immune system response, adjunctive treatment of autoimmune diseases (e.g. rheumatoid arthritis) and adjunctive treatment of cancer.
  • the present invention may further be used to treat plantar fasciitis, sprained ankles, torn knee ligaments, sciatica, teat back muscle spasm, treat torn rotator cuff, treat tennis elbow, treat carpal tunnel syndrome, treat ulnar nerve syndrome, treat temporomandibular joint syndrome, relieve pain from an abscessed tooth, accelerate growth of cultured cells or tissues, modulate cell proliferation, modulate cell differentiation, modulate cell cycle progression, modulate the expression of transforming growth factors, modulate the expression of bone morphogenetic proteins, modulate the expression of cartilage growth factors, modulate the expression of insulin-like growth factors, modulate the expression of fibroblast growth factors, modulate the expression of tumor necrosis factors, modulate the expression of interleukines
  • the present invention may also be used to retard blood and other bioproduct deterioration on storage, devitalize selected pathogens in the human or animal body, devitalize selected pathogens in isolated tissue or cell cultures, devitalize selected pathogens in blood and other bioproducts and devitalize selected pathogens in foods, beverage or other materials.
  • the compositions and methods are further illustrated by the following non-limiting examples, which are not to be construed in any way as imposing limitations upon the scope thereof. On the contrary, it is to be clearly understood that resort may be had to various other embodiments, modifications, and equivalents thereof which, after reading the description herein, may suggest themselves to those skilled in the art without departing from the spirit of the present invention and/or the scope of the appended claims.
  • the MedRelief device refers to an electrostimulator as described above for generating an electrical signal that is substantially as shown in Figure 6.
  • EXAMPLE 1 Bioelectrical Stimulation of Fractured Bones A 50 year old male was injured in a motorcycle accident that resulted in spiral fractures of his tibia and fibula. The tibia was fractured approximately 3" above the article while the fibula was fractured from the top of the bone. At the time of the accident the male was in otherwise good health and sustained no other injuries. X-rays and the evaluation in the emergency room confirmed the double fractures. It was determined that surgery to correct the problem would be required. An appointment was set for the following morning with the orthopedic surgeon. Surgery was scheduled and performed the afternoon of February 4.
  • a sterile steel nail was inserted down the shaft of the tibia running the full length of the bone. Two screws secured the nail at the top of the tibia while three screws secured it at the ankle.
  • the patient was originally scheduled for two nights in the hospital but was released approximately 24 hours following the surgery. Before release the patient was fitted with a cast walker boot for protection along with crutches and advised that he was to be non-weight bearing on the injured leg. A one week follow-up appointment was made with the surgeon. The patient returned home to rest. He was given Percocet pain relievers for pain management, taking them every four hours. By February 7th the patient was experiencing an increase in pain and an elevated temperature. The surgeon prompted treatment with antibiotics for probable injection.
  • MedReliefTM treatment bioelectrical stimulation comprising application of the waveform substantially as shown in Figure 6.
  • the wounds were cleaned of visible debris using soap and water, but no antibiotics or disinfectants were used.
  • Treatment was for about eight hours at a time, during sleep. After the first night all of the wounds were scabbed over, the areas around them swollen and painful to the touch, but the treated one was noticeably worse than the others. (It is impossible to say whether this resulted in part from the action of MedReliefTM, or simply from that wound's having been more severe in the first place.)
  • the pain and sensitivity of the treated area gradually lessened through the day, though, and by evening the three wounds all seemed about the same.
  • the treatment was repeated in the same way for a second night.
  • the MedReliefTM device was applied. More specifically, the novel waveform of the present invention as substantially as shown in Figure 6 was applied through the use of electrodes placed on the skin. A single overnight treatment during sleep took away most of the pain and stiffness, and by noon after a second overnight treatment, the knee was entirely pain-free.
  • this cycle usually lasts a lifetime. Either of the two main wrist nerves, or both, may be involved; in the subject's case it was the ulnar nerve. This form of the condition is often called "ulnar nerve syndrome.”
  • the subject started the MedRelie M treatment (comprising the application of the waveform depicted substantially as shown in Figure 6), placing one electrode pad on the edge of the affected hand and the other near the elbow so as to include the tensed muscles as well as their tendons in the current path. Treatment began at bedtime and continued through the night and the following morning. The next morning the pain was much reduced, and by early afternoon it was nearly gone, so the subject removed the unit and pads.
  • MedReliefTM the first night after the pain appeared, and halfway through the following day the pain was gone again. That time, it did not return; one night was enough.
  • EXAMPLE 6 Bioelectrical Stimulation for Alleviation of Radial Nerve Syndrome
  • the subject is a professional massage therapist whose work often requires her to apply a lot of pressure with her hands to help relax tensed muscles. Hence, she also does resistance training to help keep her arm muscles strong. After using an unfamiliar weight machine for the first time as part of her workout, the subject noticed tenderness in her left wrist. Over the next several days the wrist became progressively more swollen, stiff and painful, while the brachioradialis muscle also became chronically tensed and sore. As a result, she was forced to cancel several days of work.
  • MedReliefTM comprising the application of the waveform substantially as shown in Figure 6
  • the subject decided to try MedReliefTM (comprising the application of the waveform substantially as shown in Figure 6), beginning with one overnight treatment. Within three hours, the muscle pain was gone and her wrist pain was also quite noticeably lessened. By morning even the wrist pain was nearly gone, while the swelling was also much reduced. As a result, she was able to administer three, massages that day. The subject continued MedReliefTM treatment for two more days, twenty-four hours a day.
  • EXAMPLE 8 Bioelectrical Stimulation for Alleviation of Pain from Torn Joint Cartilage
  • the patient has suffered for many years from a torn medial meniscus (cartilage pad) in one knee, resulting in moderate to severe pain when the knee is bent, especially with a load on it as when walking down stairs.
  • the patient tried a MedRelief unit (comprising the application of the waveform substantially as shown in Figure 6), with one electrode placed on the back of the thigh, 3" above the knee and the other on the front, 2" beneath the patella.
  • Within a few minutes he reported a decrease in pain, and stated, "After 45 minutes I felt no pain. For a week after using it there was almost no pain, and now, after 2 weeks, it is still improved over my normal state.”
  • EXAMPLE 10 Bioelectrical Stimulation for Alleviation of Pain from Misaligned Vertebrae/Pinched Spinal Nerves
  • the patient has experienced severe lower back pain on previous occasions, typically on awakening following a day of golf or a long drive in his compact car.
  • the pain has responded well to chiropractic manipulation, indicating vertebral misalignment.
  • the patient had spent two days golfing, followed by a business trip for which he had to drive four hours each way in a compact car. He awoke the following morning in very severe pain that he rated at 10 ("worst imaginable") on the standard 0-10 scale.
  • Stimulation was applied with some caution, due to the usual warnings placed on electrostimulation devices not to apply them in the head or throat areas. No adverse effects were noted, however, and after about 45 minutes' treatment, the pain was relieved. It returned periodically, but further treatments of 30 to 45 minutes each time, applied in the same way, sufficed for relief. Treatment was continued through Friday, Saturday and Sunday. Upon examination on Monday, the painful tooth was found to be abscessed.
  • EXAMPLE 12 Bioelectrical Stimulation for Alleviation of Wrist Pain Due to Repetitive Motion Injury
  • the subject of this study was a secretary and began experiencing severe right wrist pain. Fearing it was the beginning of carpal tunnel, and after over the counter pain relievers had only helped temporarily, she used the invention as described herein. She wore the MedRelie M unit (enabling the application of the waveform substantially as shown in Figure 6), on her right wrist continuously for two days and then reported: "The pain began to go away within an hour of use and I only continued to wear the unit to make sure all inflammation was completely healed. I have not had any pain in my wrist in over six months.”
  • EXAMPLE 13 In Vitro Evaluation of Bioelectrical Signals The purpose of the following study is to evaluate the influence of the novel bioelectrical signals described herein on cartilage tissue.
  • Cartilage explants were prepared from fresh pig knee joints obtained from a commercial slaughterhouse. Cartilage tissue was removed from the joint using standard dissection methods. Several studies have demonstrated that such tissues retain consistent biological and mechanical properties for several days when hydrated at room temperature. When covered by appropriate media and placed in an incubator, these tissues survive for several weeks.
  • the present test configuration consisted of six-test culture wells (25 x 75 mm) connected in series via a coiled section of niobium wire. Niobium wire formed a natural coating that prevents release of metal ions from the electrodes. Before the first test chamber and after the last test chamber, there was an electrode well connected via niobium wire that effectively served to uniformly disperse the electrical field delivered to the cartilage explant test sample.
  • the cartilage samples were cut to fill approximately 75% of the well area (25 x 75 mm).
  • the thickness (1 Vz to 2 mm) of each sample had minor variations based on the specific animal and anatomic location of the sample. In all cases, the tissues were completely covered by medium. Two types of cartilage tissue were used for these experiments.
  • Normal cartilage was prepared as above and placed into test wells with no further preliminary treatment.
  • Degenerated cartilage was prepared by treating the normal cartilage for 48 hrs with IL- 1 to degrade the tissue to simulate changes observed in osteoarthritic cartilage. After 48 hours, the cartilage samples and the media were tested for the outcome variables above.
  • the outcome variables include production of proteoglycan and cartilage, release of proteoglycan, release of prostaglandin and release of nitric oxide.
  • the first three variables are measures of cartilage metabolism, and the latter two variables are measures of inflammation.
  • NCart was placed in each well of the six well system described above and treated with a MedReliefTM device with output current reduced, using external resistors, to establish a current density in the treated tissue of about 5 to 7 microamperes per square centimeter.
  • EXAMPLE 14 In Vivo Evaluation of Bioelectrical Signals The purpose of the following study is to evaluate the influence of the novel bioelectrical signals described herein on full-thickness wounds in a pig model.
  • the experimental animals are the Yorkshire farm pigs, which have skin properties (highly vascular, tight skin) similar to humans. Eight (8) one inch square; uniformly distributed, full-thickness wounds are created on the back of each pig under anesthesia. Essentially, there are four rows of two wounds starting below the shoulders and moving downwards towards the base of the spine. All animals receive appropriate pain relief post-surgery. All wounds are filled with hydrogel and covered with a Tegaderm dressing. Additional protective materials are applied to protect wounds and keep them clean. Wound dressings are changed daily. Care is used to assure a gentle wound cleaning to provide appropriate clinical care, yet give minimal disruption to the healing wound site. Wounds (8 per animal) are placed so that the centerline between
  • square-shaped wounds is about 5 inches apart from top to bottom and about 4 inches apart from side to side.
  • a template is created to assure that wound location is uniform.
  • the study endpoints are 10 and 21 days.
  • two large excisional tissue samples made completely through each wound will be collected for histological processing. It would not be safe for the animal to conduct these tissue harvests at 10 days and then have the animal survive for an additional 11 days; therefore, four original full-thickness wounds are created on day 1 and four wounds will be created on day 11, so that the animal will be sacrificed at 21 days and contain wound repairs lasting for both 10 and 21 days.
  • Several histomorphometric and immunological staining tests will be performed on these tissue samples.
  • each animal has the following evaluations: scoring by a blinded assessor on a wound healing scale of 1 to 4, photographing of wounds, and assessing Laser Doppler Perfusion.
  • the laser study consists of a series of test points surrounding each wound and using a Moor device.
  • Self-adherent, flexible, conductive electrode placement is such that each electrode pair stimulates the two wounds on each row (from top to bottom). This is accomplished by placing the electrodes centerline about two inches outside of each electrode on a row. The electrical current flowing between electrodes stimulates both wounds at the same time. Electrodes are placed on each pig only while they are in a restraining sling twice each day.
  • TXs treatments that can be studied. Each TX is applied to the eight wounds of two pigs. Therefore, there are 16 wound sites for each TX. Eight (8) of these samples are for sacrifice time 10 days, and 8 are for sacrifice time 21 days. In addition two control pigs similarly have 8 wound sites each with an inactive electrode.
  • TX1 intensity setting low ( ⁇ 5-9 mv/cm) - duration 15 minutes for each treatment
  • TX2 intensity setting low ( ⁇ 5-9 mv/cm) - duration 60 minutes for each treatment
  • TX3 intensity setting low plus resistor ( ⁇ 1-3 mv/cm) - duration 15 minutes for each treatment
  • the ulna has a diameter similar to or larger than the radius. Also, these bones are bridged by a tough interosseous membrane. Therefore, a 1 cm gap in the radius does not lead to mechanical instability. A rabbit can withstand such a bilateral procedure (one treatment and one control side) and thrive. A 1 cm gap in the radius will heal naturally beginning to show signs of healing in about 6 to 8 weeks.
  • Self-adherent, flexible, conductive electrodes are placed diametrically opposed at the wound site such that one electrode is anterior and one posterior across the bone diameter.
  • X-rays are taken to observe general rate of healing.
  • each forelimb is evaluated by Faxitron imaging and biomechanical testing to failure in torsion.
  • the electrodes are placed on both forelimbs twice each day during the post-operative study period.
  • the rabbits are placed in bunny restraints and not anesthetized each time. We anticipate significant bone fracture healing may be present in the treated animals at 4 to 6 weeks post-surgery. There are two treatments (TXs) studied.
  • mice Twice a day, animals are removed from the home cage and placed in a soft restraint device. The forelimbs are pulled through holes in the restraint and the electrodes are placed. The treated limb receives the stimulation for either approximately 30 minutes or 120 minutes.
  • the control limb has similar electrodes placed on the skin, but is not be stimulated. During the stimulation period, animals are continuously restrained for up to 120 minutes. This is considered the least invasive method for exposing the animals to the stimulation.
  • the purpose of this study is to evaluate the effects the test device on wound healing in the pig.
  • This study involves the use of Landrace-Duroc cross (farm pig) obtained from Bailey Terra Nova, Schoolcraft, Michigan.
  • the test animals are at least 10 weeks of age at arrival and weigh approximately 25 to 35 kg at study initiation. Animals selected for this study are as uniform in age and weight as possible. After a physical examination is conducted to select suitable animals for assignment to study, the animals are randomized into treatment groups using a simple randomization. Stud Desi n
  • the electrodes are placed lateral to each set of two wound twice per day for the duration indicated.
  • the electrodes are connected to the test device and the device is set as follows: Mode - Pulse, Modulation - High, and Intensity - Low. This setting delivers a pulsed stimulation between 5 and 9 mV/cm.
  • Animals in Group 4 are set up in a similar manner except that the leads have an in-line resistor designed to reduce the level of intensity to 1-3 mV/cm. Animals undergo a surgical procedure on Day 0 and Day 11 to evaluate the effects of the stimulation produced by the test device on both the acute, inflammatory stage and the longer term remodeling stage of wound healing. On Day 0 and Day 11, 4 wounds are created on the back of each animal. Wounds are paired laterally for the purpose of stimulation with the test device. c Sets of paired sites are randomized within each treatment group. A map of the treatment sites is created for each animal and included in the study data.
  • the surgical site on the dorsal right side is prepared by clipping the hair and cleansing the site with iodine scrub alternating with 70% isopropyl alcohol and painting with iodine solution. Lactated Ringer's Solution is infused during surgery via a catheter.
  • the incision sites Prior to creation of the wounds, the incision sites are marked so that each pair of wounds is approximately the same distance from the spine, and the midline of each wound is approximately 10 cm from it's pair and 12-14 cm from the next set of treatment sites.
  • the wounds are made in the shape of a square with each side being approximately 2.5 cm long. The incisions are full thickness and the tissue at the center of the square is removed.
  • the wounds are not closed, but are filled with a conductive hydrogel and covered with Tegaderm and gauze and checked daily for signs of infection.
  • the hydrogel is a product that helps to promote healing protect the wounds as well as act as a conductive agent for the stimuli.
  • the animals are closely monitored during anesthetic recovery for physiological disturbances including cardiovascular/respiratory depression, hypothermia, and excessive bleeding from the surgical/injection site. Supplemental heat is provided as needed.
  • the endotracheal tube is removed after the animal regains the swallow reflex. The animal is then returned to the study room, where postoperative monitoring continues. Long-term postoperative monitoring includes scoring of surgical sites, changing of the wound dressing daily, and administration of cephalexin (500 mg BID PO) for the duration of the study.
  • Test device implantation Route of Administration The electrodes of the test device are placed lateral to each set of paired wounds. The electrodes are placed and the treatment site stimulated twice a day for 42 days.
  • Group 2 - Low intensity (4-10 mV/cm) for approximately 60 minutes Administration of Stimulation Twice a day, animals are removed from the home cage and placed in a sling restraint. The electrodes are placed lateral to each pair of wounds and attached via the leads to the test device. The test device is activated for the required period of time and the animals may be sedated with Telazol as needed. During the stimulation period, animals are continuously restrained for up to 60 minutes. This is considered the least invasive method for exposing the animals to the stimulation.
  • Parameters evaluated include: leukocyte count (total and differential), erythrocyte count, hemoglobin, hematocrit, mean corpuscular hemoglobin, mean corpuscular volume, mean corpuscular hemoglobin concentration (calculated), absolute and percent reticulocytes, platelet count, prothrombin time, and activated partial thromboplastin time.
  • alkaline phosphatase total bilirubin (with direct bilirubin if total bilirubin exceeds 1 mg/dL), aspartate aminotransferase, alanine aminotransferase, gamma glutamyl transferase, sorbitol dehydrogenase, urea nitrogen, creatinine, total protein, albumin, globulin and A/G (albumin/globulin) ratio (calculated), glucose, total cholesterol, electrolytes (sodium, potassium, chloride), calcium and phosphorus.
  • EXAMPLE 17 In Vivo Experimentation for Evaluation of Bioelectrical Stimulation in Rat Arthritis Model The present study involves investigating the effectiveness of a novel pulse-burst electric signal substantially as described for example in Figure 6 to treat swelling, dysfunction and pain in a rat model of arthritis. Arthritis is induced in one ankle joint of a rat using the approach described by Coderre TJ, and Wall PD. (Ankle joint arthritis in rats: an alternative animal model of arthritis to that produced by Freund's adjuvant. Pain 1987; 28: 379-393: attached).
  • 0.05 ml volume of 1.5 mg of sodium urate is injected through a 21-gauge needle with its tip bevelled to 45 degree. Following the injection, the skin is closed with a single suture. Thereafter, twice a day and for about two hours each time throughout the duration of the study, the animal is anesthetized. Both hind legs are shaven. The ankle circumference is then measured on each leg. Following measurement, a self-adhesive electrode is placed on the ankle injected with urate and on the injected hip.
  • a pulse-burst electric signal is applied at subthreshold intensity for human sensation between the electrodes on the injected side for two hours, producing a current density of approximately 10 microamperes RMS per square centimeter.
  • the electrodes are removed, the leg is washed to remove any electrode residue, and the measurement is repeated.
  • the rat is then allowed to recover from anesthesia and returned to its cage until the next stimulation session. Additional measurements (see below) are taken immediately before the first stimulation session (6 hours after urate injection) and thereafter at 24,
  • Walking paw pressure Rats are observed in the above described chamber to assess the extent of the limp or alteration of gait produced by the injection of sodium urate in the hind limb.
  • Placing reflex Hand-held rats are slowly moved toward a table so that the dorsal surface of the right or left hind paw just touches the edge of the table. The response is classified as a placing reflex if the rat lifts its paw in such a way as to prepare for supporting the weight of the body on the surface. The test is repeated five times for each hind paw, and scores are based on the number of clear reflexes displayed out of 5 trials.
  • Ankle diameter The diameter of the tibio-tarsal joint in the right and left hind limbs is measured using a two-point compass and ruler. The lateral point of the compass is lined up with the talus just below the lateral malleolus of the fibula.
  • Ankle radiograph The treated and untreated tibio-tarsal joints of 2 rats are X-rayed before and 24, 48 and 72 hours after urate injection. Radiographs are used to assess the degree of soft tissue swelling as well as any destruction or decreased density of bone surrounding the ankle joint (based on prior study results, none are expected).
  • EXAMPLE 18 In Vitro Analysis Evaluating Effects of Bioelectrical Stimulation on Osteoclasts This study is designed to test the utility of imbuing osteoblasts with bioelectric signals that enhance bone-specific performance functions.
  • Human Osteoblast Cells are obtained from Clonetics (San Diego, CA) and cultured in alpha-MEM (Gibco/BRL #12561-023) with 1% Pen/Strep (Gibco/BRL #15140-015) and 10% FBS (Hyclone #A-1115-L) at 37°C in 5% C0 2 . Cells are sub-cultured every 3-4 days as follows.
  • the study compares 4 active arms with a control to evaluate the cultured cells at time intervals of 7, 14, and 21 days, evaluating: — >human osteoblasts with electro-stimulus A for 2 hours, 3 times daily ⁇ human osteoblasts with electro-stimulus B for 2 hours, 3 times daily ⁇ human osteoblasts with electro-stimulus A for 30 minutes, 3 times daily — »human osteoblasts with electro-stimulus B for 30 minutes, 3 times daily ⁇ human osteoblasts control, no stimulus
  • DNA assay Briefly, cells are removed from the cultures at day 7, 14, or 21, washed with double distilled H 2 0, and homogenized in 1.4 mL of cold 10 mM EDTA, pH 12.3. The homegates are sonicated for 10 minutes in an ice bath, incubated for 20 minutes at 37° and returned to an ice bath. A volume of 200 ⁇ l of 1 M KH 2 P0 4 is added to neutralize the pH. DNA standards are prepared from stock DNA solutions containing highly polymerized calf thymus DNA (type I, Sigma) at a concentration of 50 ⁇ g/rnL.
  • a volume of 200 ⁇ L of the standard or the homogenized sample is mixed with 1.3 mL of a 200 ng/mL Hoechst 33258-dye (Polysciences, Warrington, PA) in a 100 mM NaCl and 10 mM Tris buffer solution.
  • the fluorescence emission at 455 nm is read at an excitation wavelength of 350 nm on a fluorescence spectrophotometer.
  • ALP activity AP activity is measured with a commercially available kit
  • ALP- 10 Sigma. Cells is placed in centrifuge tube containing 1 mL of a 1M Tris solution at neutral pH and homogenized. The homogenate is further sonicated for 10 minutes in an ice bath, and a volume of 20 ⁇ L of each sample is added to 1 mL of reconstituted reagent provided by the kit at 30°C. Absorbance is measured every minute for 4 minutes at 405 nm using a HP 8452A Diode array spectrophotometer. The slope of the absorbance versus time will be used to calculate the ALP activity.
  • Osteocalcin secretion Osteocalcin secreted in the culture media is determined using a commercially available sandwich immunoassay (BT-480) from BTI (Stoughton, MA).
  • the BTI Mid-Tact Osteocalcin Elisa Kit is highly specific. It measures both the intact human osteocalcin and the major (1-43) fragment.
  • the assay is a sandwich ELISA that employs two monoclonal antibodies. One antibody (1-19) is immobilized in the wells and the second antibody (30-40) is biotinylated.
  • the assay is highly sensitive (0.5ng/ml) and requires only a 25 microliter sample. All the necessary reagents, a 96-well strip plate, and a complete 3/4 hour protocol are included with the kit.
  • Calcium deposition Calcium deposition within the culture dishes is measured by the ortho-cresolphtalein complexone procedure (Sigma Diagnostics, Procedure No. 587). Scaffolds are washed with distilled water, and placed on an orbital shaker to incubate overnight in the presence of 2 mL of 0.5 N acetic acid. Equal volumes of the calcium-binding reagent (0.024% orthocresophtalein complexone and 0.25% 8- hydroxyquinalone) and the calcium buffer (500 mmol/L 2-amino-2- methyl- 1,3 propanediol and other non-reactive stabilizers) provided in the assay kit are mixed to generate the assay working solution.
  • a volume of 300 ⁇ L of working solution is added to 10 ⁇ L of sample in a 96-well plate.
  • serial dilutions of CaCl 2 are prepared (l-250 ⁇ g/mL). The plate is incubated at room temperature for 10 minutes and then read at 575 nm. Calcium deposition from each scaffold is reported as mg Ca equivalents.
  • Synopsis This study is designed to test the utility of imbuing osteoblasts with bioelectric signals that enhance bone-specific performance functions. The study evaluates 5 conditions over 3 separate time periods. The "quick and dirty" part of the study is to evaluate alkaline phosphatase and osteocalcin as first outcome determinants. Secondary objectives seek to identify morphologic criteria, i.e. calcium deposition and tetracycline absorption as an index of matrix mineralization. Data is collected as follows:

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Abstract

L'invention concerne un appareil et un procédé de génération d'un signal électrique utilisé dans des applications biomédicales, comprenant deux générateurs d'intervalles de temporisation, entraînant chacun éventuellement un séquenceur à étapes multiples; des moyens analogues, numériques ou hybrides de combinaison des signaux temporisés obtenus en un signal électrique complexe; des moyens de filtrage optionnels de blocage du courant direct, d'élimination de composantes de fréquence sélectionnées du signal obtenu, et/ou d'augmentation de la tension si nécessaire; et des moyens conducteurs de couplage du signal obtenu au corps d'un humain ou d'un animal, à un produit alimentaire, une boisson ou un autre liquide, à une culture cellulaire ou tissulaire, ou une matière pharmaceutique, afin de soulager la douleur, stimuler la cicatrisation ou la croissance, favoriser la production de produits biochimiques spécifiques, ou dévitaliser des types d'organismes sélectionnés.
EP04755993.5A 2003-06-24 2004-06-24 Appareil et procede de stimulation bioelectrique, d'acceleration de la cicatrisation, de soulagement de la douleur ou de devitalisation d'agents pathogenes Ceased EP1648553A4 (fr)

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